CN101254090B - Fundus oculi observation device and fundus oculi image processing device - Google Patents

Fundus oculi observation device and fundus oculi image processing device Download PDF

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CN101254090B
CN101254090B CN 200810006180 CN200810006180A CN101254090B CN 101254090 B CN101254090 B CN 101254090B CN 200810006180 CN200810006180 CN 200810006180 CN 200810006180 A CN200810006180 A CN 200810006180A CN 101254090 B CN101254090 B CN 101254090B
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image
fundus
position
eye
magnification
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CN 200810006180
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Chinese (zh)
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CN101254090A (en
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木川勉
末广淳
福间康文
藤村隆
青木弘幸
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株式会社拓普康
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Priority to JP2007045831A priority patent/JP5058627B2/en
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    • GPHYSICS
    • G01MEASURING; TESTING
    • G01BMEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00Instruments as specified in the subgroups and characterised by the use of optical measuring means
    • G01B9/02Interferometers for determining dimensional properties of, or relations between, measurement objects
    • G01B9/02041Interferometers for determining dimensional properties of, or relations between, measurement objects characterised by particular imaging or detection techniques
    • G01B9/02044Imaging in the frequency domain, e.g. by using a spectrometer
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/102Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for optical coherence tomography [OCT]
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01BMEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00Instruments as specified in the subgroups and characterised by the use of optical measuring means
    • G01B9/02Interferometers for determining dimensional properties of, or relations between, measurement objects
    • G01B9/02015Interferometers for determining dimensional properties of, or relations between, measurement objects characterised by a particular beam path configuration
    • G01B9/02029Combination with non-interferometric systems, i.e. for measuring the object
    • G01B9/0203With imaging systems
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01BMEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00Instruments as specified in the subgroups and characterised by the use of optical measuring means
    • G01B9/02Interferometers for determining dimensional properties of, or relations between, measurement objects
    • G01B9/02083Interferometers for determining dimensional properties of, or relations between, measurement objects characterised by particular signal processing and presentation
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01BMEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00Instruments as specified in the subgroups and characterised by the use of optical measuring means
    • G01B9/02Interferometers for determining dimensional properties of, or relations between, measurement objects
    • G01B9/02083Interferometers for determining dimensional properties of, or relations between, measurement objects characterised by particular signal processing and presentation
    • G01B9/02089Displaying the signal, e.g. for user interaction
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01BMEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00Instruments as specified in the subgroups and characterised by the use of optical measuring means
    • G01B9/02Interferometers for determining dimensional properties of, or relations between, measurement objects
    • G01B9/02091Tomographic low coherence interferometers, e.g. optical coherence tomography
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01BMEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B2290/00Aspects of interferometers not specifically covered by any group under G01B9/02
    • G01B2290/65Spatial scanning object beam

Abstract

The invention can obtain the multiplying power of the eyeball optical system on the examined eye with high accuracy. An eyeground viewing unit (1) is an OCT unit, for detecting the interference light (LC) based on the low phase coherent light (L0), and forming an image of faults (Gi) of the eyeground (Ef) based on the detecting result. In addition, the eyeground viewing unit (1) also brings into play as the eyeground camera of for photographing the eyeground image (Ef). The image of faults or the eyeground image and the optical information (V) for displaying the eyeball optical system state of the examined eye (E) are stored in a storage part (212). A multiplying power operation part (231) operates the multiplying power of the eyeball optical system on the examined eye according to the optical information. An analysis part (232) forms the integral image according to the image of faults, and positions the integral image and the eyeground image according to the multiplying power. Moreover, the analysis part and the gauging line (L1-L3) on the eyeground image are set as the gauging devices relative to the image of faults, and figure out the layer thickness of the eyeground on the gauging position.

Description

眼底观察装置以及眼底图像处理装置 An image processing device and a fundus observation apparatus fundus

技术领域 FIELD

[0001] 本发明涉及一种用来观察眼底的眼底观察装置以及处理眼底图像的眼底图像处 [0001] The present invention relates to A method for the fundus image for fundus observation device and fundus observation fundus image processing

理装置。 Processing means.

背景技术 Background technique

[0002] 作为眼底观察装置,先前以来广泛使用眼底相机。 [0002] As a fundus observation device, since the previously widespread use of fundus cameras. 图15表示先前普通眼底相机的外观结构的一例。 15 shows a configuration of a previous one case the appearance of an ordinary fundus camera. 图16表示内设在其中的光学系统结构的一例(例如,参照日本专利特开2004-350849号公报)。 16 shows an example of the system configuration of a site in which an optical (e.g., refer to Japanese Patent Laid-Open Publication No. 2004-350849). 另外,所谓“观察”是指至少包含观察眼底的拍摄图像(另外,也可以包含通过肉眼进行的眼底观察)。 The term "observe" it refers to a captured image containing at least fundus observation (otherwise, may be included by visual observation of the fundus).

[0003] 首先,参照图15,对先前的眼底相机1000的外观结构进行说明。 [0003] First, referring to FIG. 15, the appearance of the structure of a fundus camera 1000 previously described. 该眼底相机1000 具备台架3,该台架3以可在前后左右方向(水平方向)滑动的方式搭载于基座2上。 The fundus camera 1000 includes a carriage 3, the carriage 3 is slidable manner around the horizontal direction (horizontal direction) is mounted to the base 2. 在该台架3上,设置有检测者用以进行各种操作的操作面板及控制杆4。 On the stage 3 is provided by detecting an operation panel and a control lever 4 for performing various operations.

[0004] 检测者通过操作控制杆4,而能够使台架3在基座2上自由地移动。 [0004] Detection by operating the control lever 4, so that the carriage 3 can be freely moved on the base 2. 在控制杆4的顶部,配置有要求执行眼底拍摄时而按下的操作按钮如。 At the top of the control rod 4 is arranged fundus photographing sometimes required to perform an operation button such as a press.

[0005] 在基座2上立设有支柱5,并且在该支柱5上,设置有用于载置被检测者的颚部的颚托6,及作为用以发出使受检眼E进行固视的光源的外部固视灯7。 [0005] 2 erected on the base strut 5, and on the strut 5, is provided for mounting the jaw holder 6 of the jaw portion of the test subject, and so as to emit the examinee's eye E for the fixation source external fixation lamp 7.

[0006] 在台架3上,搭载有容置存储眼底相机1000的各种光学系统和控制系统的本体部8。 [0006] On the gantry 3, a body portion mounted various optical systems and control systems of the fundus camera 1000 stores accommodating 8. 另外,控制系统可以设在基座2或台架3的内部等中,也可以设在连接于眼底相机1000 的电脑等的外部装置中。 Further, the control system may be provided inside the base 2 or the like in the gantry 3, may be provided in an external device connected to the fundus camera 1000 in computers and the like.

[0007] 在本体部8的受检眼E侧,设有和受检眼E相对向而配置的物镜部8a,在检测者侧设有目镜部8b。 [0007] In the examinee's eye E 8 side of the body portion, and is provided opposite the examinee's eye E, an eyepiece part 8b is provided on the test subject side and the objective lens part 8a disposed.

[0008] 而且,本体部8上连接有:用以拍摄受检眼E眼底的静止图像的静像摄像机9 ;及用以拍摄眼底的静止图像或动态图像的电视摄像机等摄像装置10。 [0008] Further, the connector body portion 8: still camera for capturing a still image of the fundus of the examinee's eye E 9; and an imaging apparatus for capturing a still image or dynamic image of the fundus of the television camera 10 and the like. 静像摄像机9及摄像装置10可于本体部8中进行装卸。 Still camera 9 and the imaging device 10 may be in the body portion 8 detachably.

[0009] 静像摄像机9,根据检查的目的或拍摄图像的保存方法等各种条件,可以适当交换使用搭载有CCD等摄像元件的数码相机(digital camera)、胶片相机(film camera)、一次成像相机(instant camera)等。 [0009] The still camera 9, in accordance with various conditions like object or the storage method of checking the captured image can be appropriately used interchangeably mounted imaging device like a CCD digital camera (digital camera), a film camera (film camera), an imaging camera (instant camera) and so on. 在本体部8设有安装部8c,该安装部8c用于以可更换的方式安装这样的静像摄像机9。 8 is provided in the main body portion mounting portion 8c, 8c of the mounting portion for exchangeably mounting such a manner still camera 9.

[0010] 静像摄像机9或摄像装置10为数码摄像方式的场合,可将该图像数据,传送到和眼底相机1000连接的计算机等的图像记录装置并且加以保存。 [0010] The still camera 9 or imaging device 10 is a digital camera embodiment of the case, the image data may be transferred to the image recording apparatus and a fundus camera 1000 is connected to a computer or the like and stores them.

[0011] 另外,在本体部8的检测者侧设有触摸屏11。 [0011] Further, by detecting the body portion 8 in side of the touch screen 11 is provided. 该触摸屏11上显示根据从(数字方式的)静像摄像机9或摄像装置10输出的图像信号而制作的受检眼E的眼底像。 11 displayed on the touch screen according to still camera fundus image signal (digital mode) 10 output from the imaging device 9 or fabricated from a subject eye E image. 而且,在触摸屏11上,以触摸屏11的画面中心为原点的xy坐标系重叠显示在眼底像上,当检测者触摸画面时,显示和该触摸位置对应的坐标值。 Moreover, on the touch screen 11, the touch screen 11 to the screen center as the origin of the xy coordinate system is superimposed and displayed on the fundus image, when it is detected by touching the screen, display coordinate values ​​of the touch position.

[0012] 接着,参照图16,说明眼底相机1000的光学系统的结构。 [0012] Next, with reference to FIG. 16, the configuration of the optical system of the retinal camera 1000. 眼底相机1000中设有: 照亮受检眼E的眼底Ef的照明光学系统100 ;以及将此照明光的眼底反射光导入目镜部8b、镜像摄像机9及摄像装置10中的拍摄光学系统120。 A fundus camera 1000 is provided with: illuminating a fundus Ef of the examined eye E the illumination optical system 100; and the fundus reflection light of the illumination light introducing this eyepiece portion 8b, the mirror 9 and the camera 10 photographing optical system of the imaging apparatus 120.

[0013] 照明光学系统100包含卤素灯101、聚光镜102、氙气灯103、聚光镜104、激发滤镜105及106、环形透光板107、镜片108、液晶显示器109、照明光圈110、中继透镜111、开孔镜片112、物镜113而构成。 [0013] The illumination optical system 100 comprises a halogen lamp 101, condenser lens 102, a xenon lamp 103, condenser lens 104, excitation filter 105 and 106, a ring transparent plate 107, a lens 108, a liquid crystal display 109, an illumination diaphragm 110, a relay lens 111 , the lens aperture 112, objective lens 113 is configured.

[0014] 卤素灯101为发出环境光的观察光源。 [0014] Halogen ambient observation light source 101 to emit light. 聚光镜102为用以将卤素灯101发出的环境光(观察照明光)聚光,并使该观察照明光大致均勻地照射到受检眼E(眼底Ef)的光学元件。 The condenser lens 102 is for ambient light emitted from the halogen lamp 101 (observation illumination light) condensed, and the observation illumination light substantially uniformly irradiated to the examinee's eye E (fundus Ef of) an optical element.

[0015] 氙气灯103是在对眼底Ef拍摄时进行闪光的拍摄光源。 [0015] The xenon flash lamp 103 is a photographing light source when photographing the fundus oculi Ef. 聚光镜104是用以将拍摄光源103所发出的闪光(拍摄照明光)聚光,并使拍摄照明光均勻地照射到眼底Ef的光学元件。 The condenser lens 104 is used for flash photographing (imaging illumination light) emitted by the light source 103 is condensed, and the imaging illumination light is uniformly irradiated to the optical element of the fundus oculi Ef.

[0016] 激发滤镜105、106是在对眼底Ef的眼底像进行荧光拍摄时所使用的滤镜。 [0016] The excitation filters 105 and 106 filter when the fundus image Ef fluorescence fundus imaging is used. 激发滤镜105、106分别通过螺线管(solenoid)等驱动机构而可插拔地设置在光路上。 Excitation filters 105 and 106 by a solenoid (Solenoid) as a drive mechanism disposed on the optical path pluggable. 激发滤镜105在FAG (荧光素荧光造影)拍摄时配置在光路上。 Excitation filter 105 arranged on the optical path at the time of FAG (fluorescein angiography) imaging. 另一方面,激发滤镜106在ICG (靛青绿荧光造影)拍摄时配置在光路上。 On the other hand, the excitation filter 106 arranged on an optical path when shooting in the ICG (indocyanine green fluorescent contrast). 另外,在进行彩色拍摄时,激发滤镜105、106—同从光路上退出。 In addition, during the shooting of color, with excitation filter 105,106- withdraw from the optical path.

[0017] 环形透光板107配置在和受检眼E的瞳孔共轭的位置上,并具备以照明光学系统100的光轴为中心的环形透光部107a。 [0017] The ring transparent plate 107 disposed at the pupil of the examinee's eye E and the position of the conjugate, and includes an annular light transmitting portion 107a to the optical axis of the illumination optical system 100 as the center. 镜片108使卤素灯101或氙气灯103所发出的照明光,向拍摄光学系统120的光轴方向反射。 Lens 108 so that the halogen lamp 101 or the illumination light emitted from a xenon lamp 103, reflected toward the optical axis direction of the photographing optical system 120. 液晶显示器109显示用以使受检眼E固视的固视标(未图示)。 The liquid crystal display 109 displays that the examinee's eye E for the fixation of the fixation mark (not shown).

[0018] 照明光圈110是为了防闪等而阻挡一部分照明光的光圈构件。 [0018] The illumination diaphragm 110 is a diaphragm member in order to prevent flash like blocking part of the illumination light. 该照明光圈110可以在照明光学系统100的光轴方向上移动,因此,可以改变眼底Ef的照明区域。 The illumination diaphragm 110 may be moved in the optical axis direction of the illumination optical system 100, thus, may change the illumination area of ​​the fundus Ef.

[0019] 开孔镜片112是将照明光学系统100的光轴和拍摄光学系统120的光轴合成的光学元件。 [0019] The opening 112 is a lens optical axis of the optical element 100 of the illumination optical system and the photographing optical system 120 synthesis. 在开孔镜片112的中心区域开有孔部112a。 Opening 112 in the central area of ​​the lens opening hole portion 112a. 照明光学系统100的光轴和拍摄光学系统120的光轴在该孔部11¾的大致中心位置交叉。 The optical axis of the illumination system optical axis 100 and the photographing optical system 120 cross at substantially the center of the hole portion 11¾ position. 物镜113设在本体部8的物镜部8a 内。 An objective lens 113 provided in the lens portion 8a of the body portion 8.

[0020] 具有这样结构的照明光学系统100,是以下面所述的形态照亮眼底Ef。 [0020] The illumination optical system 100 having such a structure, the following form is illuminated fundus Ef. 首先,在观察眼底时,点亮卤素灯101,输出观察照明光。 First, at the time of fundus observation, the halogen lamp 101 is lit, the illumination light output was observed. 该观察照明光经过聚光镜102、104而照射环形透光板107。 This observation illumination light is irradiated through a condenser lens 102, an annular light-transmissive plate 107. 通过环形透光板107的环形透光部107a的光由镜片108所反射,且经过液晶显示器109、照明光圈110及中继透镜111,并由开孔镜片112沿着拍摄光学系统120的光轴方向被反射,经物镜113聚焦而射入受检眼E,照亮眼底Ef。 Transmitting plate by an annular light transmitting portion 107a of the loop 107 is reflected by the mirror plate 108, and through the liquid crystal display 109, the illumination diaphragm 110 and the relay lens 111 by the lens 112 along the optical axis of the aperture of the photographing optical system 120 direction is reflected, focused by the objective lens 113 and is incident on the examinee's eye E, to illuminate the fundus Ef.

[0021] 此时,由于环形透光板107配置在和受检眼E的瞳孔共轭的位置上,因此在瞳孔上形成射入受检眼E的观察照明光的环状像。 [0021] At this time, since the ring transparent plate 107 disposed at the pupil of the examinee's eye E and the position of the conjugate, thereby forming incident on the examinee's eye E is observed as an annular illumination light on the pupil. 射入的观察照明光的眼底反射光,通过瞳孔上的环形像的中心暗部而从受检眼E射出。 Fundus reflection light of the observation illumination light is incident, the light emitted from the examinee's eye E through the central dark part of the ring image on the pupil.

[0022] 另一方面,在拍摄眼底Ef时,氙气灯103进行闪光,且拍摄照明光通过同样的路径而照射到眼底Ef。 [0022] On the other hand, when photographing the fundus oculi Ef, a xenon flash lamp 103, and the imaging illumination light is irradiated onto the fundus oculi Ef through the same path. 当进行荧光拍摄时,根据是进行FAG拍摄还是进行ICG拍摄,而使激发滤镜105或106选择性地配置在光路上。 When fluorescence photography, is according to FAG imaging or ICG imaging performed, the excitation filter 105 or 106 is selectively disposed in the optical path.

[0023] 其次,拍摄光学系统120包含物镜113、开孔镜片112(的孔部11¾)、拍摄光圈121、阻挡滤镜122及123、倍率可变透镜124、中继透镜125、拍摄透镜126、快速复原反射镜片(quick return mirror) 127及拍摄媒体9a而构成。 [0023] Next, the photographing optical system 120 includes an objective lens 113, the lens aperture 112 (hole portion 11¾), imaging diaphragm 121, barrier filters 122 and 123, a variable magnification lens 124, relay lens 125, imaging lens 126, the quick return mirror plate (quick return mirror) 127 and the imaging media 9a is configured. 另外,拍摄媒体9a是静像摄像机9的拍摄媒体(CCD、相机胶卷、一次成像胶卷等)。 Furthermore, the photographing media 9a is a photographing media still camera 9 (the CCD, camera film, a film image, etc.).

[0024] 通过受检眼E的瞳孔上形成的环状像的中心暗部而射出的照明光的眼底反射光, 通过开孔镜片112的孔部11¾而入射到拍摄光圈121。 The fundus reflection light of the illumination light [0024] an annular image formed on the pupil of the examinee's eye E through the central dark part of the light emitted by the lens opening hole portion 112 enters the photographing diaphragm 121 11¾. 开孔镜片112反射照明光的角膜反射光,并且不使角膜反射光混入到射入拍摄光圈121的眼底反射光中。 The lens apertures 112 cornea reflected light of the illumination light and the reflected light is not mixed into the cornea imaging the fundus reflection light is incident on the diaphragm 121. 以此,可抑制观察图像或拍摄图像上产生闪烁(flare)。 In this, flicker is generated (FLARE) on the observation image or the captured image can be suppressed.

[0025] 拍摄光圈121是形成有大小不同的多个圆形透光部的板状构件。 [0025] The photographing diaphragm 121 is formed with a plurality of different sizes of circular plate-like light transmitting member portions. 多个透光部构成光圈值(F值)不同的光圈,通过未图示的驱动机构,选择性地将一个透光部配置在光路上。 A plurality of light-transmitting portions constitute different iris aperture value (F value), by a drive mechanism (not shown), a light transmitting portion selectively disposed in the optical path.

[0026] 阻挡滤镜122、123通过螺线管等的驱动机构而可插拔地设置在光路上。 [0026] The barrier filters 122 and 123 by a drive mechanism such as a solenoid pluggable disposed on the optical path. 在进行FAG拍摄时,使阻挡滤镜122配置在光路上。 During FAG imaging, the barrier filter 122 is disposed on the optical path. 在进行ICG拍摄时,使阻挡滤镜123插在光路上。 During ICG imaging, the barrier filter 123 is inserted in the optical path. 而且,在进行彩色拍摄时,阻挡滤镜122、123—同从光路上退出。 Further, when performing color imaging, the barrier filter 122,123- same exit from the optical path.

[0027] 倍率可变透镜IM可以通过未图示的驱动机构而在拍摄光学系统120的光轴方向上移动。 [0027] The variable magnification lens IM by unillustrated drive means is moved in the optical axis direction of the photographing optical system 120. 以此,可以变更观察倍率或拍摄倍率,并可以进行眼底像的聚焦等。 With this, you can change the observation magnification or shooting magnification, and can be focused fundus image and so on. 拍摄透镜126 是使来自受检眼E的眼底反射光在拍摄媒体9a上成像的透镜。 Photographing lens 126 is reflected from the fundus of the examinee's eye E in the imaging lens imaging light on the medium 9a.

[0028] 快速复原反射镜片127设置成可以通过未图示的驱动机构而绕着旋转轴127a进行旋转。 [0028] The quick return mirror plate 127 can be provided by a drive mechanism (not shown) is rotated around the rotation axis 127a. 当以静像摄像机9进行眼底Ef的拍摄时,将斜设在光路上的快速复原反射镜片127向上方掀起,而将眼底反射光引导向拍摄媒体9a。 When photographing the fundus oculi Ef at a still camera 9, the swash provided in the quick-return mirror plate 127 off the optical path upwardly, and the fundus reflected light guided to the imaging media 9a. 另一方面,当通过摄像装置10进行眼底拍摄时或通过检测者的肉眼进行眼底观察时,快速复原反射镜片127斜设配置在光路上,从而使眼底反射光朝向上方反射。 On the other hand, when the fundus observation by photographing a fundus imaging device 10, or by visual inspection person, the quick return mirror plate 127 disposed on the optical path as obliquely arranged, so that the reflected light toward the fundus reflected upward.

[0029] 拍摄光学系统120中更设有用以对由快速复原反射镜片127所反射的眼底反射光进行导向的向场透镜(视场透镜)128、切换镜片129、目镜130、中继透镜131、反射镜片132、拍摄透镜133及摄像元件10a。 [0029] The photographing optical system 120 is provided to more 129, an eyepiece 130, a relay lens 131 facing field lens (field lens) 128, is guided by the lens switching the quick return mirror plate 127 of the fundus reflected light, a reflective lens 132, imaging lens 133 and an imaging device 10a. 摄像元件IOa是内设于摄像装置10中的CXD等摄像元件。 The imaging element is internally provided IOa CXD imaging device 10 and the like in the imaging device. 在触摸屏11上,显示由摄像元件IOa所拍摄的眼底图像Ef。 11 on the touch screen, displaying a fundus image Ef by the imaging element IOa captured.

[0030] 切换镜片1¾和快速复原反射镜片127同样,能够以旋转轴129a为中心而旋转。 [0030] handover 1¾ lens and the quick return mirror plate 127 Similarly, the rotation shaft 129a can be rotated centering. 该切换镜片1¾在通过肉眼进行观察时斜设在光路上,从而反射眼底反射光而将其引导向目镜13。 The switching lens 1¾ when viewed by the naked eye obliquely disposed on the optical path so as to reflect the fundus reflection light which is guided to the eyepiece 13.

[0031] 另外,在通过摄像装置10拍摄眼底图像时,切换镜片1¾从光路退出。 [0031] Further, when the fundus image captured by the imaging device 10, the switching 1¾ lens retracted from the optical path. 眼底反射光透过中继透镜131、镜片132、拍摄透镜133,而在摄像元件IOa上成像,并且使眼底图像Ef'显示在触摸屏11上。 The fundus reflection light passes through the relay lens 131, a lens 132, imaging lens 133, and on the imaging element IOa of, and the fundus image Ef 'displayed on the touch screen 11.

[0032] 此种眼底相机1000,是用以观察眼底Ef的表面,即观察视网膜的表面的眼底观察装置。 [0032] Such a fundus camera 1000, is to observe the surface of the fundus oculi Ef, i.e., the surface of the fundus oculi observation device to observe the retina. 另一方面,视网膜的深层存在视细胞层或视网膜色素上皮层等层,而且在较深的部分存在脉络膜或巩膜此种组织,而近年来,观察该些深层组织的装置之实用化已有进步(例如参照日本专利特开2003-543号公报、日本专利特愿2004-52195号公报、日本专利特表2004-502483 号公报)。 On the other hand, the presence of deep cell layer of the retina or retinal pigment epithelium layer and the like, and choroid or sclera exist in the deeper part of such an organization, but in recent years, the plurality of observed practical means of deep tissues has been progress (e.g., refer to Japanese Patent Laid-open Publication No. 2003-543, Japanese Unexamined Patent Publication No. 2004-52195, Japanese Unexamined Patent Publication No. 2004-502483).

[0033] 在日本专利特开2003-543号公报、日本专利特愿2004-52195号公报、日本专利特表2004-50M83号公报中所揭示的眼底观察装置是应用了所谓OCT (Optical Coherence Tomography,光学相干断层成像)技术的装置(也称为光图像计测装置、光学相干拓扑仪装置等)。 [0033] In Japanese Patent Laid-Open Publication No. 2003-543, Japanese Unexamined Patent Publication No. 2004-52195, Japanese Patent Laid fundus oculi observation device table Publication No. 2004-50M83 disclosed is the use of so-called OCT (Optical Coherence Tomography, ) means optical coherence tomography (also referred to as an optical image measurement device, an optical coherence topology instrument device, etc.). 这样的眼底观察装置是将低相干光分成两部分,将其中一部分(信号光)引导向眼底,将另一部分(参照光)引导向预定的参照物体,并且根据将经由眼底的信号光以及被参照物体反射的参照光加以重叠而获得的干涉光,形成眼底表面至深层组织的断层图像。 Such a fundus oculi observation device is a low-coherence light into two parts, in which a portion (signal light) is guided to the fundus, another portion (reference light) guided predetermined reference object to, and in accordance with the signal light through the fundus and a reference reference light reflected by the object to be superimposed interference light obtained by forming a tomographic image of a fundus surface to deeper tissues. [0034] 日本专利特表2004-502483号公报所揭示的眼底观察装置具有用四分圆来呈现眼底的层厚度的功能。 A fundus observation device [0034] Japanese Unexamined Patent Publication No. 2004-502483 disclosed by the quadrant has a function of presenting the thickness of the layer of the fundus. 眼底的层厚度在例如青光眼诊断等中被视为重要信息。 The layer thickness of the fundus is considered an important information in diagnosis of glaucoma and the like, for example.

[0035] 在评价眼底的层厚度时,广泛实行的是:如图17所示,在眼底上设定圆形计测线, 分析沿着各计测线的断层图像以计测层厚度。 [0035] In the evaluation of the layer thickness of the fundus, it is widely practiced: 17, set in a circular measurement lines on the fundus to analyze tomographic image along the respective measurement lines in a layer thickness measurement. 圆形计测线M1、M2、M3分别具有半径ml、m2、 m3。 Circular measurement lines M1, M2, M3 each having a radius ml, m2, m3. 半径ml、m2、m3例如分别设定为1. 2mm、1. 6mm、2. 0mm。 Radius ml, m2, m3, for example, are set to 1. 2mm, 1. 6mm, 2. 0mm. 另外,计测线Ml、M2、M3设定成同心圆状,其中心C设定在视神经乳头的中心位置。 Further, the measurement line Ml, M2, M3 is set concentrically with its center C is set at the center position of the optic nerve head.

[0036] 像这样评价眼底的层厚度时,有时会产生由受检眼的眼球光学系统引起的计测误差。 [0036] When the layer thickness of the image of the fundus such evaluation, measurement error may occur due to the optical system of the eye of the examinee's eye. 也就是说,眼球光学系统对照射到眼底的光的影响在每一个受检眼中是不同的,先前, 并不考虑此个人差异而设定各计测线Ml、M2、M3。 That is, the optical system of the eye fundus irradiated to influence the light in each of the eyes of the subject are different, the previous, does not take this into account individual differences in each set measuring line Ml, M2, M3. 因此,难以准确地设定正规的位置,也就是距离视神经乳头的中心C的半径ml、m2、m3的位置。 Thus, it is difficult to accurately set the normal position, i.e. the position of the optic nerve from the radius center C teat ml, m2, m3 of.

[0037] 先前,计测线M1、M2、M3是以如下方式设定的。 [0037] Previously, the measurement lines M1, M2, M3 is set in the following manner. 首先,事先计测受检眼的眼球光学系统的屈光度数或眼轴长度。 Firstly, the eyeball optical system measured beforehand meter examinee's eye or the axial length of refraction. 其次,使用该计测结果和古尔斯特兰德(Gullstrand)模型眼的水晶体的屈光力,推算受检眼的角膜曲率。 Next, using the measurement results and the refractive power of the Gullstrand (the Gullstrand) crystal body model eye, corneal curvature estimating the examinee's eye. 然后,使用该推算值等来计算眼球光学系统的倍率。 Then, using this calculated estimated value or the like of the optical system magnification of the eye. 接着,使用该倍率值来决定半径ml、m2、m3,以设定各计测线M1、M2、M3。 Next, using the ratio value to determine the radius of ml, m2, m3, to set the respective measurement lines M1, M2, M3.

[0038] 然而,在所述方法中,由于是使用基于模型眼的标准值,因此难以准确地求出该受检眼的倍率。 [0038] However, in the method, since the standard value is based model eye, it is difficult to accurately obtain the magnification of the examinee's eye. 所以,难以在该受检眼的相关的正规位置上设定计测线M1、M2、M3。 Therefore, it is difficult to set the measurement lines M1, M2, M3 in the normal position of the associated eye of the subject.

[0039] 另外,眼球光学系统的倍率影响不仅在评价眼底的层厚度时存在,而且在考虑眼底上的位置或距离时也一直存在。 [0039] Further, the magnification of the optical system of the eye affect not only evaluate the presence of the layer thickness of the fundus, and in consideration of the position or distance has been present on the fundus.

[0040] 本发明是为了解决如上的问题研发而成的,其目的在于,提供一种可以准确地求出受检眼的眼球光学系统的倍率的眼底观察装置以及眼底图像处理装置。 [0040] The present invention is made to solve the above problem research and development from its object is to provide a fundus observation apparatus to accurately obtain a fundus image processing apparatus and a magnification of the optical system of the eye of the examinee's eye.

发明内容 SUMMARY

[0041] 为了达成所述目的,本发明的第一方面是一种眼底观察装置,其特征在于包括:图像形成元件,利用拍摄光学系统的拍摄,以光学方式取得数据,形成受检眼眼底的断层图像;存储元件,存储了显示所述受检眼的眼球光学系统状态的光学信息;运算元件,根据所述光学信息来运算所述眼球光学系统的倍率并运算所述拍摄光学系统的倍率;以及分析元件,包含计测位置设定元件,设定所述眼底的计测位置,且所述分析元件根据所述眼球光学系统的倍率与所述拍摄光学系统的倍率来分析所述断层图像,并求出由所述计测位置设定元件所设定的所述计测位置的所述眼底的层厚度。 [0041] In order to achieve the above object, a first aspect of the present invention is a fundus observation device comprising: an image forming element, an optical imaging by the imaging system to obtain data optically to form a fundus of the examinee's eye tomographic image; storage element stores the eyeball optical system of an optical information display state of the examinee's eye; computing element, according to the optical information calculates the magnification of the optical system of the eye and calculates the photographing magnification of the optical system; and an analysis element, comprising a measuring position setting member sets the fundus measuring position, and the analysis element to analyze the tomographic image according to the magnification of the optical system of the eye and the magnification of the photographing optical system, and obtaining the fundus setting the measuring element by the position measuring position set by the layer thickness.

[0042] 而且,本发明的第二方面是一种眼底图像处理装置,其特征在于包括:存储元件, 存储受检眼眼底的断层图像、及显示所述受检眼的眼球光学系统状态的光学信息;运算元件,根据所述光学信息来运算所述眼球光学系统的倍率;以及分析元件,包含计测位置设定元件,设定所述眼底的计测位置,且所述分析元件根据所述倍率来分析所述断层图像,并求出由所述计测位置设定元件所设定的所述计测位置的所述眼底的层厚度。 [0042] Further, a second aspect of the present invention is a fundus image processing apparatus, comprising: a storage element stores the tomographic image of the examinee's eye fundus, and a display optical system of the eye of the examinee's eye optical state information; computing element, according to the optical information calculates the magnification of the optical system of the eye; and analyzing elements, comprising a measuring position setting member sets the fundus measuring position, and the analysis element according to the magnification analyze the tomographic image, and obtains the measurement position of the fundus element is set by the position of the measuring set of layer thicknesses.

[0043][发明的效果] [0043] [Effect of the Invention]

[0044] 根据本发明,可以根据显示受检眼的眼球光学系统状态的光学信息,来运算该眼球光学系统的倍率,并根据该经运算的倍率来分析受检眼的断层图像。 [0044] According to the present invention, an optical information eyeball optical system of the examinee's eye displayed state, calculates the magnification of the optical system of the eye, and to analyze the tomographic image of the examinee's eye based on the magnification by the operation. 由此,不需要像先前那样使用古尔斯特兰德模型眼的屈光力来推算受检眼的角膜曲率等基于该受检眼固有信息以外的信息来进行运算处理。 Thus, as the refractive power does not need to use as previously Gullstrand eye model to calculate the curvature of the cornea of ​​the examinee's eye based on information other than the unique information of the examinee's eye performs arithmetic processing. 因此,可以根据各受检眼来高精度地求出眼球光学系统的倍率。 Thus, it is possible to accurately obtain the magnification of the optical system of the eye according to each of the examinee's eye. 附图说明 BRIEF DESCRIPTION

[0045] 图1是表示本发明的眼底观察装置较佳的实施形态的整体结构的一例的概略结构图。 [0045] FIG. 1 is a schematic configuration diagram showing an example of the overall configuration of a preferred embodiment of the fundus oculi observation device according to the present invention.

[0046] 图2是表示本发明的眼底观察装置较佳的实施形态中内设在眼底相机单元内的扫描单元的结构的一例的概略结构图。 [0046] FIG. 2 is a schematic configuration diagram showing an example of a configuration of a fundus observation device according to the present invention, the preferred embodiment features the scanning unit in the fundus camera unit.

[0047] 图3是表示本发明的眼底观察装置较佳的实施形态中OCT单元的结构的一例的概略结构图。 [0047] FIG. 3 is a schematic configuration diagram showing an example of configuration of a fundus oculi observation device according to the present invention, the preferred embodiment of the OCT unit.

[0048] 图4是表示本发明的眼底观察装置较佳的实施形态中运算控制装置的硬件结构的一例的概略方框图。 [0048] FIG. 4 is a schematic block diagram showing a hardware configuration of the apparatus of the fundus oculi observation device according to the present invention, the preferred embodiment arithmetic control.

[0049] 图5是表示本发明的眼底观察装置较佳的实施形态的控制系统结构的一例的概略方框图。 [0049] FIG. 5 is a schematic block diagram showing a control system configuration of the preferred embodiment of the fundus oculi observation device according to the present invention.

[0050] 图6是表示本发明的眼底观察装置较佳的实施形态中操作面板的外观结构的一个例子的概略图。 [0050] FIG. 6 is a schematic view showing an example of the external configuration of the fundus oculi observation device according to the present invention, the preferred embodiment of the operation panel.

[0051] 图7是表示本发明的眼底观察装置较佳的实施形态中运算控制装置的功能性结构的一例的概略方框图。 [0051] FIG. 7 is a schematic block diagram showing a functional configuration of the apparatus of the fundus oculi observation device according to the present invention, the preferred embodiment arithmetic control.

[0052] 图8是表示本发明的眼底观察装置较佳的实施形态的信号光的扫描形态的一例的概略图。 [0052] FIG. 8 is a schematic view showing an example of the scanning signal light form the preferred embodiment of the fundus oculi observation device according to the present invention. 图8(A)表示从信号光相对于受检眼的入射侧观察眼底时的信号光的扫描形态的一例。 FIG 8 (A) shows an example of a signal from the examinee's eye is viewed incident light when scanning form signal light with respect to the fundus. 而且,图8(B)表示各扫描线上扫描点的排列形态的一例。 Further, FIG. 8 (B) shows an example of an array pattern of each scanning line of the scanning spot.

[0053] 图9是表示本发明的眼底观察装置较佳的实施形态的信号光的扫描形态、以及沿着各扫描线而形成的断层图像形态的一例的概略图。 [0053] FIG. 9 is a scanning form signal light in the preferred embodiment of the fundus oculi observation device according to the present invention, and a schematic view showing an example of the form of a tomographic image along each scanning line is formed.

[0054] 图10是表示本发明眼底观察装置的较佳实施形态的使用形态的一个例子的流程图。 [0054] FIG. 10 is a flowchart showing an example of the use form of the preferred embodiment of the fundus oculi observation device according to the present invention.

[0055] 图11是表示本发明眼底观察装置的较佳实施形态所显示的显示画面的一个例子的概略图。 [0055] FIG. 11 is a schematic view showing an example of a display screen of the preferred embodiment of the fundus oculi observation device according to the present invention is shown.

[0056] 图12是表示本发明眼底观察装置的较佳实施形态所显示的显示画面的一个例子的概略图。 [0056] FIG. 12 is a schematic view showing an example of a display screen of the preferred embodiment of the fundus oculi observation device according to the present invention is shown.

[0057] 图13是表示本发明眼底观察装置的较佳实施形态所显示的显示画面的一个例子的概略图。 [0057] FIG. 13 is a schematic view showing an example of a display screen of the preferred embodiment of the fundus oculi observation device according to the present invention is shown.

[0058] 图14是表示本发明眼底观察装置的较佳实施形态所显示的显示画面的一个例子的概略图。 [0058] FIG. 14 is a schematic view showing an example of a display screen of the preferred embodiment of the fundus oculi observation device according to the present invention is shown.

[0059] 图15是表示先前的眼底观察装置(眼底相机)的外观结构的一例的概略侧面图。 [0059] FIG. 15 is a schematic side view showing an example of the external configuration of the fundus oculi observation device previously (fundus camera).

[0060] 图16是表示先前的眼底观察装置(眼底相机)的内部结构(光学系统的结构) 的一例的概略图。 [0060] FIG. 16 is a fundus observation device previously (fundus camera) of an internal configuration (optical system configuration) is a schematic diagram showing an example.

[0061] 图17是表示用来计测眼底的层厚度的计测位置的设定形态的一个例子的概略图。 [0061] FIG. 17 is a schematic view showing an example of setting the aspect of measuring position for measuring the thickness of the layer of the fundus.

[0062] 1 :眼底观察装置 IA :眼底相机单元 [0062] 1: a fundus observation device IA: retinal camera unit

[0063] 2:基座 3:台架[0064] 3a :操作面板 4 :控制杆[0065] 4a :操作按钮 5:支柱[0066] 6:颚托 7 :外部固视视灯[0067] 8 :本体部 8a :物镜部[0068] 8b :目镜部 8c :安装部[0069] 9 :静像摄像机 9a :拍摄媒体[0070] 10、12 :摄像装置 10a、12a :摄像元件[0071] 11 :触摸屏 100:照明光学系统[0072] 101 :光源 102、104 :聚光镜[0073] 103 :氙气灯 105、106 :激发滤镜[0074] 107 :环形透光板 107a :环形透光部[0075] 108 :镜片 109 :液晶显示器[0076] 110 :照明光圈 111、125、131 :中继透镜[0077] 112:开孔镜片 112a :孔部[0078] 113 :物镜 120 :拍摄光学系统[0079] 121 :拍摄光圈 122、123 :阻挡滤镜[0080] 124 :倍率可变透镜 126、133、138 :拍摄透镜[0081] 127 :快速复原反射镜片 128 :向场透镜(视场透[0082] 129 :切换镜片 130 :巨镜[0083] 132 :反射镜片 134、136 :分色镜[0084] 135 :半透型反射镜 137 [0063] 2: a base 3: stage [0064] 3a: operation panel 4: lever [0065] 4a: an operation button 5: Pillar [0066] 6: the chin rest 7: external fixation lamp view [0067] 8 : a body portion 8a: an objective lens unit [0068] 8b: eyepiece portion 8C: mounting portion [0069] 9: still camera 9a: imaging medium [0070] 10, 12: image pickup means 10a, 12a: imaging element [0071] 11: touch screen 100: an illumination optical system [0072] 101: light source 102: a condensing lens [0073] 103: xenon lamp 105: excitation filter [0074] 107: 107a ring transparent plate: an annular light transmitting portion [0075] 108 : lens 109: liquid crystal display [0076] 110: illuminating aperture 111,125,131: a relay lens [0077] 112: lens opening 112a: hole [0078] 113: lens 120: photographing optical system [0079] 121: photographing aperture 122, 123: blocking filter [0080] 124: variable magnification lens 126,133,138: photographing lens [0081] 127: quick return mirror plate 128: lens [0082] 129 to the field lens (field of view: switch lens 130: giant mirror [0083] 132: reflection mirror 134, 136: dichroic mirror [0084] 135: transflective reflector 137 、141C、141D :反射镜[0085] 139、142 :透镜 140 =LCD[0086] 141 :扫描单元 141AU41B :检流计镜[0087] 141a、141b :旋转轴 150 =OCT 单元[0088] 151 :连接部 152 :连接线[0089] 152a、161、163、164、165 :光纤 152b :端面[0090] 160 :低相干光源 162 :光耦合器[0091] 171、181 :准直透镜 172 :玻璃块[0092] 173 :密度滤镜 174 :参照镜片[0093] 180 :分光仪 182 :衍射光栅[0094] 183 :成像透镜 184 =CCD[0095] 200 :运算控制装置 200a :总线[0096] 201 :微处理器 202 :RAM[0097] 203 =ROM 204 :硬盘驱动器[0098] 204a :控制程序 205 :键盘[0099] 206 :鼠标 207 :显示器[0100] 208:图像形成板 208a:眼底图像形成板[0101] 208b =OCT图像形成板 209:通信接口(I/F)[0102] 210 :控制部 211 :主控制部[0103] 212 :存储部 220 :图像形成部[0104] 230 :图像处理部 231 :倍率运算部[0105] 232 :分析部 233 :积分图像形成部[0106] 234 :定位 , 141C, 141D: reflector [0085] 139,142: a lens 140 = LCD [0086] 141: scanning unit 141AU41B: galvanometer mirror [0087] 141a, 141b: rotary shaft 150 = OCT unit [0088] 151: connection 152: connection line [0089] 152a, 161,163,164,165: the optical fiber 152b: end surface [0090] 160: low coherence light source 162: optical coupler [0091] 171, 181: a collimator lens 172: glass block [ 0092] 173: density filter 174: Referring to the lens [0093] 180: 182 spectrometer: the diffraction grating [0094] 183: an imaging lens 184 = CCD [0095] 200: arithmetic control unit 200a: a bus [0096] 201: microprocessor is 202: RAM [0097] 203 = ROM 204: a hard disk drive [0098] 204a: the control program 205: keyboard [0099] 206: mouse 207: display [0100] 208: image forming board 208a: fundus image forming board [0101] 208b = OCT image forming board 209: a communication interface (I / F) [0102] 210: control unit 211: main control unit [0103] 212: storage unit 220: an image forming portion [0104] 230: The image processing section 231: magnification calculation unit [0105] 232: analysis unit 233: the integral image forming unit [0106] 234: Location 235 :计测位置设定部[0107] 236 :层厚计测部 240 :用户接口[0108] 240A :显示部 240Β :操作部[0109] 241、242 :镜片驱动机构 243 :参照镜片驱动机构[0110] 244 :浓度滤镜驱动机构 301 :菜单键[0111] 302 :裂像键 303 :拍摄光量键[0112] 304 :观察光量键 305 :颚托键[0113] 306 :拍摄键 307 :变焦键[0114] 308 :图像切换键 309 :固视标切换键[0115] 310 :固视标位置调整键 311 :固视标尺寸切换键[0116] 312 :模式切换旋钮 1000 :眼底相机[0117] C :中心 E :受检眼[0118] Ef:眼底 Ef:眼底图像[0119] Gi(i = 1〜m):断层图像 H:图像区域[0120] Ll〜L4:层位置图像 M1、M2、M3 :计测线[0121] ml、m2、m3 :半径 P:鼠标指针[0122] Q:点图像 Ri(i = 1〜m):扫描线[0123] Rij (i = 1 〜m, j = 1 〜η) :扫描点RE :扫描结束位置[0124] RS :扫描开始位置 Sl〜S14 :步骤 235: a measurement position setting unit [0107] 236: a layer thickness measuring section 240: a user interface [0108] 240A: a display unit 240Β: the operation unit [0109] 241: lens driving means 243: Referring to the lens driving mechanism [ 0110] 244: concentration filter drive mechanism 301: the menu key [0111] 302: split image key 303: photographing light amount button [0112] 304: observation light volume key 305: chin rest key [0113] 306: capture key 307: a zoom key [0114] 308: image switch button 309: fixation target switch button [0115] 310: fixation target position adjusting key 311: fixation target size switching button [0116] 312: mode switching knob 1000: the retinal camera [0117] C : central E: examinee's eye [0118] Ef: fundus Ef of: fundus image [0119] Gi (i = 1~m): tomographic image H: image region [0120] Ll~L4: layer position images M1, M2, M3 : measurement line [0121] ml, m2, m3: radius P: mouse pointer [0122] Q: dot image Ri (i = 1~m): a scanning line [0123] Rij (i = 1 ~m, j = 1 ~η): scan point RE: scanning end position [0124] RS: scanning start position Sl~S14: step

具体实施方式 Detailed ways

[0125] 参照图式,对本发明的眼底观察装置以及眼底图像处理装置的较佳实施形态的一例进行详细说明。 [0125] Referring to the drawings, an example of preferred embodiment of the fundus oculi observation device according to the present invention and a fundus image processing apparatus will be described in detail. 另外,对和图15、图16所示的先前同样的构成部分,使用和这些图相同的符号来表示。 In addition, and FIG. 15, the same elements as previously, and the same reference numerals used in these figures shown in FIG. 16 to FIG.

[0126][装置结构] [0126] [Apparatus configuration]

[0127] 首先,参照图1〜图7说明本实施形态的眼底观察装置的结构。 [0127] First, referring to FIG. 1 ~ 7 illustrates the structure of a fundus observation device according to the present embodiment. 在此,图1表示本实施形态的眼底观察装置1的整体结构的一个例子。 Here, FIG. 1 shows an example of the overall configuration of the apparatus 1 of the present embodiment fundus observation. 图2表示眼底相机单元IA内的扫描单元141的结构的一个例子。 FIG 2 shows an example of a configuration of the scanning unit 141 in a fundus camera unit IA. 图3表示OCT单元150的结构的一个例子。 3 shows an example of the configuration of the OCT unit 150. 图4表示运算控制装置200的硬件结构的一个例子。 Figure 4 shows an example of a hardware configuration of the arithmetic control device 200. 图5表示眼底观察装置1的控制系统的结构的一个例子。 FIG. 5 shows an example of the configuration of a control system of the fundus observation device 1. 图6表示设置在眼底相机单元IA内的操作面板3a的结构的一个例子。 FIG 6 shows an example of a configuration of a fundus camera unit disposed in the operation panel 3a of the IA. 图7表示运算控制装置200的控制系统结构的一个例子。 FIG. 7 shows an example of the system configuration of a control operation of the control device 200.

[0128][整体结构] [0128] [Entire Structure]

[0129] 如图1所示,本实施形态的眼底观察装置1包含具有和图15、图16的眼底相机相同功能的眼底相机单元1A、存储光图像计测装置(OCT装置)的光学系统的OCT单元150、 执行各种运算处理或控制处理等的运算控制装置200而构成。 [0129] 1, the present embodiment comprises a fundus oculi observation device 1 and 15, a fundus camera 16 of the retinal camera unit the same function. 1A, the optical image measurement device is stored (OCT apparatus) of the optical system OCT unit 150, performs various arithmetic processes or control processes such as arithmetic and control unit 200 is configured.

[0130] 连接线152的一端安装在OCT单元150上。 End [0130] Cable 152 is mounted on the OCT unit 150. 该连接线152的另一端上安装有连接部151。 The connection line 151 is attached to the other end of the connecting portion 152. 该连接部151安装在眼底相机单元IA的框体安装部(参照图15的装着部8c)。 Frame mounting portion (see FIG filled portion 8c 15) mounted on the connecting portion 151 of the fundus camera unit IA. 而且,在连接线152的内部导通有光纤。 Furthermore, the inner conductor connection line 152 through an optical fiber. OCT单元150和眼底相机单元IA经过连接线152而光学性连接。 OCT unit 150 and the retinal camera unit via the connection line 152 IA optically connected. 另外,也可以在眼底相机单元IA的框体内部设置OCT单元150的光学系统。 Further, means may be provided OCT optical system 150 is inside the housing of the fundus camera unit IA.

[0131][眼底相机单元的结构] [0131] [Configuration of retinal camera unit]

[0132] 眼底相机单元IA是利用摄像装置10、12来拍摄眼底表面的二维图像的装置。 [0132] IA retinal camera unit 10, 12 is a device to capture a two-dimensional image of the fundus by the imaging device surface. 眼底相机单元IA具有和图15所示先前的眼底相机1000大致相同的外观结构。 IA and retinal camera unit having a fundus camera 1000 shown previously in FIG. 15 is substantially the same external configuration. 而且,眼底相机单元IA和图16所示先前的光学系统同样具备:照明光学系统100,对受检眼E的眼底Ef 进行照明;以及拍摄光学系统120,将该照明光的眼底反射光引导向摄像装置10。 Further, the fundus camera unit 16 previously shown in FIG. IA and an optical system also includes: an illumination optical system 100, on examinee's eye E, the fundus Ef is illuminated; and an imaging optical system 120, and the fundus reflection light of the illumination light guided to the imaging device 10.

[0133] 另外,在后面会详述,本实施形态的拍摄光学系统120的摄像装置10检测具有近红外区域的波长的照明光。 [0133] Further, will be described in detail later, the image pickup apparatus 10 according to the present embodiment, the detection of the photographing optical system 120 has an illumination light having a wavelength near-infrared region. 而且,在该拍摄光学系统120中,另外设有摄像装置12,用以检测具有可见光区域的波长的照明光。 Further, in this imaging optical system 120, the imaging device 12 is additionally provided for detecting the illumination light having a wavelength in the visible light region. 另外,拍摄光学系统120将由OCT单元150发出的信号光引导到眼底Ef,并且将经过眼底Ef的信号光引导到OCT单元150。 Further, the signal 120 by the imaging optical system of the OCT unit 150 emits light to the fundus oculi Ef, and guide the OCT unit 150 through the fundus oculi Ef of the signal light.

[0134] 另外,照明光学系统100和先前同样包含观察光源101、聚光镜102、拍摄光源103、 聚光镜104、激发滤镜105及106、环形透光板107、镜片108、液晶显示器109、照明光圈110、 中继透镜111、开孔镜片112、物镜113而构成。 [0134] Further, the illumination optical system 100 and the previous likewise comprises an observation light source 101, condenser lens 102, an imaging light source 103, condenser lens 104, excitation filter 105 and 106, a ring transparent plate 107, a lens 108, a liquid crystal display 109, an illumination diaphragm 110 , a relay lens 111, the lens aperture 112, objective lens 113 is configured.

[0135] 观察光源101输出包含波长例如约400nm〜700nm的范围的可见光区域的照明光。 [0135] comprising an observation light source 101 outputs the illumination light such as visible light wavelength region is the range of about 400nm~700nm. 另外,拍摄光源103输出包含波长例如约700nm〜SOOnm的范围的近红外区域的照明光。 The imaging light source 103 outputs the illumination light including a wavelength range of, for example, near-infrared region of about 700nm~SOOnm. 该拍摄光源103输出的近红外光,设定成较在OCT单元150中使用的光的波长短(后面再述)。 Near-infrared light output from the imaging light source 103, the light is set to be used more in the short wavelength OCT unit 150 (described later again).

[0136] 而且,拍摄光学系统120包含物镜113、开孔镜片112(的孔部11¾)、拍摄光圈121、阻挡滤镜122及123、倍率可变透镜124、中继透镜125、拍摄透镜126、分色镜134、向场透镜(视场透镜)128、半透型反射镜135、中继透镜131、分色镜136、拍摄透镜133、摄像装置10 (摄像元件10a)、反射镜片137、拍摄透镜138、摄像装置12 (摄像元件12a)、透镜139、 及LCD (Liquid Crystal Display,液晶显示器)而构成。 [0136] Further, the photographing optical system 120 includes an objective lens 113, the lens aperture 112 (hole portion 11¾), imaging diaphragm 121, barrier filters 122 and 123, a variable magnification lens 124, relay lens 125, imaging lens 126, a dichroic mirror 134, the imaging field lens (field lens) 128, a transflective mirror 135, relay lens 131, dichroic mirror 136, a lens 133, an imaging device 10 (imaging device 10a), a reflective lens 137, imaging lens 138, the imaging device 12 (imaging device 12a), a lens 139 and LCD (liquid crystal display, a liquid crystal display) is configured.

[0137] 在本实施形态的拍摄光学系统120中,和图16所示的先前的拍摄光学系统120 不同,设有分色镜134、半透型反射镜片135、分色镜136、反射镜片137、拍摄透镜138、透镜139 及LCD140。 [0137] In the present embodiment, the imaging optical system 120, as shown in FIG. 16 and the previous different photographing optical system 120, dichroic mirror 134 is provided, the transflective type reflective lens 135, dichroic mirror 136, the mirror plate 137 , photographing lens 138, a lens 139 and LCD 140.

[0138] 分色镜134为用以反射照明光学系统100发出的照明光的眼底反射光(包含波长约400nm〜SOOnm的范围),并且为可供由OCT单元150发出的信号光LS(包含波长约800nm-900n范围,后述)透过的构造。 [0138] The dichroic mirror 134 to the fundus reflection light of the illumination light to reflect emitted from the illumination optical system 100 (comprising a wavelength range of about 400nm~SOOnm), and for the signal light LS is emitted from the OCT unit 150 (including a wavelength range from about 800nm-900n, to be described later) through the structure.

[0139] 另外,分色镜136可通过由照明光学系统100输出的具有可见光区域的波长的照明光(由观察光源101输出的波长约400nm〜700nm的可见光),并可反射具有近红外区域的波长的照明光(由拍摄光源103输出的波长约700nm〜800nm的近红外光)。 [0139] Further, the dichroic mirror 136 through the illumination light having a wavelength of the visible light region 100 outputs an illumination optical system (wavelength output from the observation light source 101 of about 400nm~700nm visible light), and reflecting near-infrared region the wavelength of the illumination light (wavelength outputted from the imaging light source 103 of about 700nm~800nm ​​near-infrared light).

[0140] 在IXD140中显示有为了使受检验E固视的固视标(内部固视标)等。 [0140] In IXD140 displayed in order to make the fixation of the examinee E fixation mark (internal fixation target) or the like. 由该IXD140 发出的光经透镜139聚光后,由半透型反射镜135反射,通过向场透镜1¾反射到分色镜136。 After the light is emitted from the lens IXD140 139 is condensed by the transflective reflective mirror 135, reflected by the dichroic mirror 1¾ field lens 136. 然后,通过拍摄透镜126、中继透镜125、倍率可变透镜124、开孔镜片112(的孔部112a)、物镜113等,射入受检眼E。 Then, the photographing lens 126, a relay lens 125, the magnification variable lens 124, the lens aperture 112 (hole portion 112a), the objective lens 113, etc., is incident on the examinee's eye E. 由此,该内部固视标等投影到受检眼E的眼底Ef。 Accordingly, the internal fixation target, etc. is projected onto the fundus oculi Ef of the eye E of the examinee.

[0141] 摄像元件IOa为内藏在电视摄像机等的摄像装置10内的C⑶或CMOS等的摄像元件,特别是检测近红外区域的波长的光(即摄像装置10为检测近红外光的红外线电视摄像机)。 [0141] IOa imaging element is incorporated in the image pickup element or the like C⑶ CMOS imaging device 10 in the television camera or the like, in particular, detecting light having a wavelength near-infrared region (i.e., the imaging device 10 detects the near infrared light is an infrared TV camera). 摄像装置10输出图像信号,作为检测近红外光的结果。 The imaging device 10 outputs an image signal as a result of detecting near-infrared light.

[0142] 触摸屏11依据该图像信号显示眼底Ef的表面的二维图像(眼底图像Ef ')。 [0142] The touch screen 11 displays a two-dimensional image of the surface of the fundus oculi Ef (fundus image Ef ') based on the image signal. 而且,该图像讯号被送到运算控制装置200,在其显示器(后述)中显示眼底图像。 Further, the image signal is sent to the arithmetic and control unit 200, the fundus image displayed on its display (described later).

[0143] 另外,使用该摄像装置10拍摄眼底时,例如,可利用由照明光学系统100的拍摄光源103输出的近红外区域波长的照明光。 [0143] Further, when photographing the fundus 10 of the image pickup apparatus using, for example, photographing illumination light source 103 output by the illumination optical system 100 of the near-infrared wavelength region.

[0144] 另一方面,摄像元件1¾为内藏在电视摄像机等的摄像装置12中的CXD或CMOS 等的摄像元件,特别是检测可见光区域波长的光(即摄像装置12为检测可见光的电视摄像机)。 [0144] On the other hand, is incorporated in the imaging element 1¾ CXD or CMOS image pickup element or the like of the imaging device in the television camera 12 and the like, in particular, the detection light in the visible wavelength region (i.e., the visible light imaging apparatus 12 to detect a television camera ). 该摄像装置12输出图像信号,作为检测可见光的结果。 12 an output image signal of the image pickup apparatus, as a result of detecting visible light.

[0145] 触摸屏11依据该图像讯号显示眼底Ef的表面的二维图像(眼底图像Ef ')。 [0145] The touch screen 11 displays a two-dimensional image of the surface of the fundus oculi Ef (fundus image Ef ') based on the image signal. 另外,该图像信号被送到运算控制装置200,在其显示器(后述)中显示眼底图像。 Further, the image signal is sent to the arithmetic and control unit 200, the fundus image displayed on its display (described later).

[0146] 另外,使用该摄像装置12拍摄眼底时,例如,可利用从照明光系统100的观察光源101输出的可见光区域波长的照明光。 [0146] Further, when photographing the fundus 12 of the image pickup apparatus using, for example, with illumination light having a wavelength in the visible region of the observation light source 101 outputs an illumination system 100.

[0147] 本实施形态中的拍摄光学系统120中设有扫描单元141及透镜142。 [0147] The present embodiment, photographing optical system 120 is provided in the scanning unit 141 and a lens 142. 扫描单元141 具备如下结构,即,用以扫描自OCT单元150输出的光(后述信号光LS)对眼底Ef的照射位置。 The scanning unit 141 includes a structure in which, for scanning the light output from the OCT unit 150 (described later signal light LS) on the irradiation position of the fundus oculi Ef.

[0148] 透镜142使来自OCT单元150的信号光LS通过连接线152,引导成为平行光束,并将其射入扫描单元141。 [0148] lens 142 makes the signal light LS from the OCT unit 150 through the connection line 152, the guide into a parallel beam, and is incident on the scanning unit 141. 而且,透镜142的作用为使经过扫描单元141而来的信号光LS的眼底反射光聚光。 Moreover, the action of the lens 142 such that the scanning unit 141 through the signal light LS from the fundus reflection light condensed.

[0149] 图2中表示扫描单元141的具体结构的一例。 In [0149] FIG. 2 shows an example of a specific configuration of the scanning unit 141. 扫描单元141包含检流计镜(galvanometer mirror) 141AU41B 以及反射镜片141C、141D 而构成。 The scanning unit 141 includes a galvanometer mirror (galvanometer mirror) 141AU41B and a reflective lenses 141C, 141D is configured.

[0150] 检流计镜141A、141B设为可以分别以旋转轴141a、141b为中心而旋转的反射镜。 [0150] galvanometer mirrors 141A, 141B may be respectively set to the rotation shaft 141a, 141b as the center of rotation of the mirror. 各检流计镜141A、141B通过后述的驱动机构(图5所示的镜片驱动机构241、242),分别以旋转轴141a、141b为中心而旋转,分别变更其反射面(把信号光LS反射的面)的方向,即检流计镜141A、141B的位置。 Each galvanometer mirror 141A, a drive mechanism (lens driving mechanism 241, 242 shown in FIG. 5) described later after 141B, respectively, to the rotation shaft 141a, 141b and the center of rotation, which are changed reflecting surface (the signal light LS direction of the reflection surface), i.e., a galvanometer mirror 141A, 141B of the position.

[0151] 旋转轴141a、141b以相互正交的方式而配设。 [0151] the rotation shaft 141a, 141b so as to be disposed perpendicular to each other. 在图2中,检流计镜141A的旋转轴141a配设为平行于该图的纸面,且检流计镜141B的旋转轴141b配设为垂直于该图的纸面。 In FIG. 2, the galvanometer mirror 141A is set with the rotary shaft 141a parallel to the drawing of the figure, and the rotation axis galvanometer mirror 141b 141B feature set perpendicular to the paper surface of FIG.

[0152] S卩,检流计镜141B可以向图2中的两侧箭头所示方向旋转,检流计镜141A可以向垂直于该两侧箭头的方向旋转。 [0152] S Jie, a galvanometer mirror 141B can be rotated in the direction indicated by arrow in FIG. 2 on both sides, a galvanometer mirror 141A can be rotated in the direction perpendicular to the sides of arrow. 以此,一对检流计镜141A、141B分别发挥作用,使信号光LS 的反射方向变更为相互正交的方向。 In this, the pair of galvanometer mirrors 141A, 141B, respectively, play a role in the reflection direction of the signal light LS changes to a direction orthogonal to each other. 从图1、图2可以明白,当使检流计镜141A旋转时,信号光LS在χ方向上扫描,而当使检流计镜141B旋转时,信号光LS在y方向上扫描。 From FIG. 1, FIG. 2 will be understood that, when the galvanometer mirror 141A is rotated, the signal light LS in a scanning direction χ, whereas when the galvanometer mirror 141B is rotated, the scanning signal light LS in the y direction.

[0153] 由检流计镜141A、141B所反射的信号光LS,向和由反射镜片141C、141D所反射而入射至检流计镜141A时相同的方向行进。 [0153] by a galvanometer mirror 141A, 141B of the reflected signal light LS, and a reflective lenses 141C, 141D are reflected to the same direction incident on the galvanometer mirrors 141A travels.

[0154] 另外,如上所述,连接线152的内部导通有光纤152a。 [0154] As described above, the internal conductive line 152 are connected to the optical fiber 152a. 该光纤15¾的端面152b是和透镜142相对而配设。 The end face of the optical fiber 15¾ 142 and the lens 152b is disposed oppositely. 从该端面152b所射出的信号光LS朝向透镜142使束径逐渐放大而行进,但通过该透镜142而成为平行光束。 Toward the lens 142 from the signal light LS emitted from this end face 152b so that the beam diameter is enlarged gradually travels, but rather through the lens 142 into a parallel beam. 相反,经由眼底Ef的信号光LS通过透镜142 而朝向端面152b聚光,被导入到光纤15加。 In contrast, the signal light LS via the fundus oculi Ef converging toward the end face 152b by the lens 142, the optical fiber 15 is introduced into the add.

[0155] [OCT单元O结构] [0155] [OCT unit structure O]

[0156] 接着,参照图3说明OCT单元150的结构。 [0156] Next, with reference to FIG. 3 illustrates the structure 150 of the OCT unit. 该图所示的OCT单元150是一种装置, 其是用来根据光学取得的数据(利用后述的CCD184检测出的数据)形成眼底的断层图像。 It is shown in the figure OCT unit 150 is a device which is used to form a tomographic image of the fundus based on the data (the CCD 184 described later data detected) optical achieved. [0157] 此OCT单元150具备和先前的光图像计测装置大致相同的光学系统。 [0157] This and the previous OCT unit 150 includes an optical image measurement device is substantially the same optical system. 亦即OCT单元150具备:干涉计,将从光源输出的光分割成参照光和信号光,将经过参照物体的参照光和经过被测定物体(眼底Ef)的信号光进行重叠,以产生干涉光;以及检测该干涉光,并将作为检测结果的信号(检测信号)输出到运算控制装置200的元件。 I.e. OCT unit 150 comprises: an interferometer output light from the light source into reference light and signal light, the light passes through the reference object reference signal object to be measured (fundus Ef of) light overlap to generate an interference light ; and detecting the interfering light, and outputs the signal as a detection result (detection signal) to the arithmetic and control unit 200 of the element. 运算控制装置200分析该检测信号,由此形成被测定物体(眼底Ef)的断层图像。 200 analyzes the detection signal operation control means, thereby forming a tomographic image of the object to be measured (fundus Ef of) a.

[0158] 低相干光源160是由输出低相干光LO的超辐射二极管(SLD,superluminescent diode)或发光二极管(LED,light-emitting diode)等的宽带光源所构成。 [0158] low coherence light source 160 is a low-coherence light LO output from a superluminescent diode (SLD, superluminescent diode) or a light emitting diode (LED, light-emitting diode) composed of a broadband light source or the like. 该低相干光LO 例如为具有近红外区域的波长、并且具有数十微米左右的时间性相干长度的光。 The low-coherence light LO is, for example having a wavelength in the near infrared region, and light having several tens of micrometers temporal coherence length.

[0159] 低相干光LO具有比眼底相机单元IA的照明光(波长约400nm〜SOOnm)更长的波长,例如含有约800nm〜900nm范围的波长。 Illumination light (wavelength of about 400nm~SOOnm) longer wavelength [0159] low-coherence light LO than the retinal camera unit IA, for example, the wavelength range comprising about 800nm~900nm.

[0160] 从低相干光源160所输出的低相干光L0,例如通过由单模光缆(single-mode fiber)或保偏光纤(polarization maintaining fiber)所构成的光纤161,被引导向光耦合器(coupler) 162。 [0160] from the low-coherence light source 160 output from the low coherence light L0, for example by a single-mode fiber (single-mode fiber), or PM fiber (polarization maintaining fiber) constituting the optical fiber 161 is guided to an optical coupler ( coupler) 162. 光耦合器162将该低相干光源LO分割为参照光LR和信号光LS。 The optical coupler 162 LO low coherence light source is divided into reference light LR and signal light LS.

[0161] 另外,光耦合器162具有光分割元件(分光器,plitter)及光重叠元件(耦合器, coupler)双方的功能,在此,习惯性地称为“光耦合器”。 [0161] Further, the optical coupler 162 having a light dividing element (beam splitter, plitter) superimposed element and a light (coupler, Coupler) both functions, in this case, habitually called "optical coupler."

[0162] 由光耦合器162产生的参照光LR,被由单模光纤等构成的光纤163引导,从光纤端面射出。 [0162] reference light LR generated by the optical coupler 162, is emitted from the optical fiber 163 composed of a single mode fiber guided from the other end face of the optical fiber. 所射出的参照光LR通过准直透镜171,成为平行光束后,经过玻璃块172及密度滤镜173,由参照镜174(参照物体)所反射。 After the reference light LR emitted by the collimator lens 171 into a parallel beam, through a glass block 172 and a density filter 173, the reference mirror 174 (reference object) reflected.

[0163] 由参照镜片174所反射的参照光LR再次经过密度滤镜173及玻璃块172,并通过准直透镜171而在光纤163的光纤端面上聚光。 [0163] Referring to the lens 174 by the reference light LR reflected through the density filter 173 and the glass block 172 again, and by the collimator lens 171 converging in the fiber end face of the optical fiber 163. 所聚光的参照光LR通过光纤163而被引导向光耦合器162。 The converging reference light LR is guided by an optical fiber 163 to optical coupler 162.

[0164] 在此,玻璃块172及密度滤镜173,是作为用以使参照光LR和信号光LS的光路长度(光学距离)一致的延迟元件而发挥作用,而且作为用以使参照光LR和信号光LS的色散特性一致的色散补偿元件而发挥作用。 [0164] Here, the glass block 172 and a density filter 173, as the optical path length (optical distance) identical to the delay elements of the reference light LR and the signal light LS is to function, but as for reference light LR and uniform dispersion characteristics of the signal light LS dispersion compensation elements play a role.

[0165] 而且,密度滤镜173也发挥使参照光光量减少的减光滤镜的作用,例如由旋转型ND(Neutral Density,中性密度)滤镜构成。 [0165] Further, the density filter 173 also play a reduced amount of light of the reference light reduction filter effect, for example, a rotary ND (Neutral Density, neutral density) filter configuration. 此密度滤镜173通过包含马达等的驱动装置的驱动机构(后述的密度滤镜驱动机构M4,参照图5),而被旋转驱动,借此发挥使参照光LR的光量的减少量改变的作用。 This density filter 173 by a drive mechanism (to be described later density filter drive means M4, with reference to FIG. 5) includes a motor driving device or the like, is driven to rotate, thereby reducing the amount of play that the light amount of the reference light LR is changed effect. 以此,可以改变利于干涉光LC产生的参照光LR的光量。 This may be beneficial to change the light amount of the reference light LR interference light LC is generated.

[0166] 另外,参照镜174为可沿参照光LR的行进方向(图3所示的两侧箭头方向)移动的结构。 [0166] Further, the reference mirror 174 along the traveling direction of the reference light LR (the direction shown by the arrow in both FIG. 3) to move the structure. 借由这样的结构,能够确保和受检眼E的眼轴长度相对应的参照光LR的光路长度。 By means of such a configuration, it is possible to ensure that the subject eye E and the axial length corresponding to the optical path length of the reference light LR. 参照镜174的移动可利用含有马达等的驱动装置的驱动机构(后述的参照镜片驱动机构对3,参照图5)进行。 Moving the reference mirror drive mechanism 174 may be utilized such as a motor driving device comprising (described later with reference to the lens driving mechanism 3 with reference to FIG. 5).

[0167] 另一方面,由光耦合器162产生的信号光LS,由单模光纤等构成的光纤164引导至连接线152的端部。 [0167] On the other hand, the signal light LS generated by the optical coupler 162, is guided by an optical fiber 164 composed of a single mode fiber to the other end of the connecting line 152. 在连接线152的内部导通有光纤15加。 The inner conductor connection line 152 through an optical fiber 15 increase. 此处,光纤164和光纤15¾ 可以由单一光纤构成,另外,也可以是将各个端面接合而一体形成的光纤。 Here, the optical fiber 164 and the optical fiber may be constituted by a single optical fiber 15¾, further, may be bonded to each end face of the optical fiber are integrally formed. 总之,光纤164、 152a只要可以在眼底相机单元IA和OCT单元150之间传送信号光LS即可。 In short, the optical fiber 164, 152a as long as the transmit signal 150 to the fundus camera unit IA and the OCT unit light LS.

[0168] 信号光LS在连接线152内部被引导而被导向到眼底相机单元1A。 [0168] the signal light LS is guided within the connection line 152 and guided to the retinal camera unit 1A. 再者,信号光LS 经过透镜142、扫描单元141、分色镜134、拍摄透镜126、中继透镜125、倍率可变透镜124、 拍摄光圈121、开孔镜片112的孔部11¾和物镜113,而入射到受检眼E。 Further, the signal light LS passes through the lens 142, the scanning unit 141, the dichroic mirror 134, imaging lens 126, relay lens 125, the magnification variable lens 124, the photographing diaphragm 121, a lens opening hole portion 11¾ 112 and objective lens 113, incident on the examinee's eye E. 另外,使信号光LS入射到受检眼E时,阻挡滤镜122、123分别事先从光路中退出。 Further, the signal light LS enters into the examinee's eye E, the barrier filters 122 and 123 are retracted from the optical path in advance.

[0169] 入射到受检眼E的信号光LS在眼底(视网膜)Ef上成像并反射。 [0169] the signal light LS enters into the eye E imaged subject and reflected on the fundus (retina) Ef. 此时,信号光LS 不仅被眼底Ef的表面反射,也到达眼底Ef的深部区域并在屈光率边界上产生散射。 At this time, the signal light LS is not only reflected by the surface of the fundus oculi Ef, but also reaches the deep area of ​​the fundus oculi Ef and the refractive scattering at the rate boundaries. 因此, 经过眼底Ef的信号光LS成为包含反映眼底Ef的表面形态的信息、及反映在眼底Ef的深部组织的屈光率边界的背后散射(backscattering)的状态的信息的光。 Thus, the signal light LS via the fundus oculi Ef contains information reflecting the surface morphology becomes the fundus oculi Ef, the reflected light information and state scattering refractive power behind the boundary of the deep tissue of the fundus oculi Ef (Backscattering) a. 将该光简称为“信号光LS的眼底反射光”。 The light abbreviated as "fundus reflection light of the signal light LS."

[0170] 信号光LS的眼底反射光在眼底相机单元IA的所述路径上反向前进,在光纤15¾ 的端面152b上聚光,通过光纤152入射到OCT单元150,并通过光纤164而返回到光耦合器162。 [0170] the signal light LS advances fundus reflection light on the reverse path of the fundus camera unit IA, condensed on the end face 152b of the optical fiber 15¾ enters the OCT unit 150 through the optical fiber 152, and returns to the optical fiber 164 by optocoupler 162.

[0171] 光耦合器162使经由眼底Ef而返回的信号光LS和由参照镜片174所反射的参照光LR重叠,产生干涉光LC。 [0171] 162 optical coupler of the signal light LS returning through the fundus oculi Ef and the reference lens 174 by the overlap of the reflected reference light LR, generating an interference light LC. 所产生的干涉光LC通过单模光纤等构成的光纤165,被引导向分光仪180。 LC interference light generated by an optical fiber 165 composed of a single mode fiber and the like, is guided to the spectrometer 180.

[0172] 另外,本实施形态中采用的是迈克尔逊型干涉仪(Michelsoninterferometer)JS 也可以适当采用例如马赫-曾德(Mach-khnder)型等任意类型的干涉仪。 [0172] Further, the present embodiment uses a Michelson interferometer (Michelsoninterferometer) JS may be appropriately employed, for example, a Mach - Zehnder any type (Mach-khnder) type interferometer and the like.

[0173] 分光仪(spectrometer) 180是以包含准直透镜181、衍射光栅182、成像透镜183 和CCD(Charge Coupled Device,电荷耦合器件)184而构成。 [0173] spectrometer (spectrometer) 180 is comprises a collimator lens 181, a diffraction grating 182, an imaging lens 183 and CCD (Charge Coupled Device, charge-coupled device) 184 is configured. 本实施形态的衍射光栅182 是使光透过的透过型衍射光栅,但当然也可以使用使光反射的反射型衍射光栅。 A diffraction grating 182 of the present embodiment is a transmission-type diffraction grating that transmits light, but of course also possible to use the reflection type diffraction grating light reflection. 而且,当然也可以应用其它光检测元件来代替(XD184。 Also, of course, it may also be used in place of other light detecting element (XD184.

[0174] 入射到分光仪180的干涉光LC通过准直透镜181而成为平行光束之后,被衍射光栅182分光(频谱分解)。 After [0174] the interference is incident to the spectroscope 180 and the LC light into a parallel beam by the collimator lens 181, beam splitter 182 is a diffraction grating (spectral decomposition). 所分光的干涉光LC通过成像透镜183而在(XD184的摄像面上成像。CCD184接收该干涉光LC并转换为电检测信号,将该检测信号输出到运算控制装置200。 The spectral interference light LC is received by the imaging lens 183 (XD184 imaging surface of the imaging .CCD184 interference light LC and converts to electrical detection signals, the detection signal to the arithmetic and control unit 200.

[0175][运算控制装置的结构] [0175] [Configuration of the arithmetic control device]

[0176] 其次,说明运算控制装置200的结构。 [0176] Next, the configuration of the arithmetic control device 200. 此运算控制装置200分别相当于本发明的“眼底图像处理装置”和“计算机”的一个例子。 This arithmetic and control unit 200 correspond to an example of the "fundus image processing apparatus" and "computer" in the present invention.

[0177] 运算控制装置200进行以下处理:对从OCT单元150的分光仪180的(XD184所输入的检测信号进行分析,形成受检眼E的眼底Ef的断层图像。此时的分析方法和先前的傅立叶OCT方法是相同的。 [0177] arithmetic and control unit 200 performs the following process: for (XD184 detection signal input from the spectrometer 150 of the OCT unit 180 analyzes a tomographic image of the fundus Ef is formed of the examinee's eye E at this time and the previous analysis. Fourier OCT method is the same.

[0178] 而且,运算控制装置200进行如下处理:依据由眼底相机单元IA的摄像装置10、 12输出的图像信号,形成表示眼底Ef的表面(视网膜)的形态的二维图像(的图像数据)。 [0178] Further, the arithmetic control unit 200 performs processing: two-dimensional image showing the surface morphology of the fundus oculi Ef (retina) (image data) 10 based on the image signal from the imaging means of the retinal camera unit 12 outputs IA is formed .

[0179] 另外,运算控制装置200执行眼底相机单元IA以及OCT单元150的各部分的控制。 [0179] Further, the arithmetic control unit 200 executes control of each part of the retinal camera unit IA and OCT unit 150.

[0180] 作为眼底相机单元IA的控制,例如,进行观察光源101或拍摄光源103的照明光的输出控制、激发滤镜105及106或阻挡滤镜122及123在光路上的插入/退出动作的控制、LCD140等显示装置的动作的控制、照明光圈110的移动控制(光圈值的控制)、拍摄光圈121的光圈值的控制、倍率可变透镜124的移动控制(倍率的控制)等。 [0180] As a control the retinal camera unit IA, for example, observation light source 101 outputs the illumination control source 103 or imaging, excitation filters 105 and 106 or the barrier filters 122 and 123 is inserted into the optical path in / out operation a display control operation of the control apparatus, etc. LCD 140, the movement control (control of the diaphragm value), the photographing control aperture value of the diaphragm 121, the movement control variable magnification lens 124 (controlling the magnification), etc. of the illumination diaphragm 110. 另外,运算控制装置200对扫描单元141内的检流计镜141A、141B的动作(反射面方向的变更动作)进行控制。 In addition, a galvanometer mirror in the scanning unit 141A of the operational control means 141,200, 141B operation (operation of changing the direction of the reflection surface) is controlled.

[0181] 另外,作为运算控制装置200对OCT单元150的控制,例如,进行低相干光源160 的低相干光LO的输出控制、参照镜174的移动控制、密度滤镜的旋转动作(参照光LR的光量的减少量的变更动作)的控制、CCD184的蓄积时间的控制等。 [0181] Further, as the control unit 200 pairs of OCT arithmetic control device 150, e.g., a control output low coherence light source 160 of low coherence light LO is, referring to the movement control, the rotational operation of the density filter 174 of the mirror (reference light LR the reduced amount of the light amount changing operation) control, control of the accumulation time of CCD184.

[0182] 参照图4,对像这样作用的运算控制装置200的硬件结构的一个例子进行说明。 [0182] Referring to FIG 4, an example of a hardware configuration of the arithmetic control unit such as function 200 will be described.

[0183] 运算控制装置200具备和先前的电脑同样的硬件结构。 [0183] and the arithmetic and control unit 200 includes a previous same computer hardware configuration. 具体来说,是以包含微处理器201 (CPU、MPU 等)、RAM202、R0M203、硬盘驱动器(HDD, Hard Disk Driver) 204、键盘205、鼠标206、显示器207、图像形成板208及通信接口(I/F)209而构成。 Specifically, based on includes a microprocessor 201 (CPU, MPU, etc.), RAM202, R0M203, a hard disk drive (HDD, Hard Disk Driver) 204, a keyboard 205, mouse 206, display 207, the image forming panel 208 and a communication interface ( I / F) 209 is configured. 以上各部分是通过总线200a而连接。 The above portions are connected via a bus 200a.

[0184] 微处理器201将存储在硬盘驱动器204中的控制程序20½展开到RAM202上,以此在本实施形态中执行特征性动作。 [0184] The microprocessor 201 control program stored in the hard disk drive 204 is 20½ to expand the RAM202, in order to perform the characteristic operation of the present embodiment.

[0185] 而且,微处理器201执行所述装置各部分的控制、或各种运算处理等。 [0185] Further, the microprocessor 201 executes control of each part of the device, various arithmetic processing or the like. 而且,执行和来自键盘205或鼠标206的操作信号对应的装置各个部分的控制、显示器207的显示处理的控制、通信接口209的各种数据或控制信号等的发送接收处理的控制等。 Further, control of transmission and reception processing control respective portions of the device to perform a corresponding operation signal from a keyboard 205 and a mouse 206, a display control process of the display 207, various data or communication interface 209 control signals.

[0186] 键盘205、鼠标206及显示器207是作为眼底观察装置1的用户接口而使用的。 [0186] keyboard 205, a mouse 206 and a display 207 as a fundus observation device 1 of the user interface using well. 键盘205是作为用以键入字符或数字等的设备而使用。 Keyboard 205 is used as a device for typing characters or numbers and the like. 鼠标206是作为用以对显示器207的显示画面进行各种输入操作的设备而使用。 Mouse 206 is used as the display screen of the display 207 to perform various input operations of the device.

[0187] 而且,显示器207是例如由LCD(Liquid Crystal Display,液晶显示器)或CRT (Cathode Ray Tube,阴极射线管)显示器等构成任意的显示设备。 [0187] Also, display 207 is any display device composed of, for example, by a LCD (Liquid Crystal Display, a liquid crystal display) or CRT (Cathode Ray Tube, a cathode ray tube) display or the like. 显示器207显示由眼底观察装置1所形成的眼底Ef的图像等各种图像,或显示操作画面或设定画面等各种画面。 Display 207 displays various images like the fundus oculi Ef of an apparatus formed by the fundus observation, an operation screen or display various screens or setting screens and the like.

[0188] 另外,眼底观察装置1的用户接口并不限定于这样的结构,也可以使用例如轨迹球(track ball)、控制杆、触摸面板式IXD、用于眼科检查的控制面板等具备显示输出各种信息的功能以及输入各种信息执行装置操作的功能的任意用户接口机构而构成。 [0188] In addition, the user interface of the fundus observation device 1 is not limited to such a configuration, for example, may be a trackball (track ball), a lever, a touch panel of formula IXD, for ophthalmic examination control panel includes a display output functions of the various input information, and various functions performed by apparatus operation information of any user interface mechanism is configured.

[0189] 图像形成板208为处理形成受检眼E的眼底Ef的图像(图像数据)的专用电子电路。 The image (image data) [0189] The image forming board 208 is a process of forming a fundus Ef of the eye E of the examinee dedicated electronic circuits. 在该图像形成板208中设有眼底图像形成板208a及OCT图像形成板208b。 In this image forming board 208 is provided with a fundus image forming board 208a and OCT image forming board 208b.

[0190] 眼底图像形成板208a是进行动作以根据来自眼底相机单元IA的摄像装置10或摄像装置12的图像信号来形成眼底图像的图像数据的专用电子电路。 [0190] fundus image forming board 208a is an operation signal to the image pickup device 10 or the imaging device 12 from the fundus camera unit IA is formed according to electronic circuitry dedicated image data of the fundus image.

[0191] 又,OCT图像形成板20¾是进行动作以根据来自OCT单元150的分光仪180的CCD184的检测信号来形成眼底Ef的断层图像的图像数据的专用电子电路。 [0191] and, 20¾ OCT image forming board is operated according to a detection signal from the spectrometer 150 of the OCT unit 180 CCD184 dedicated electronic circuit formed tomographic image of the fundus Ef of the image data.

[0192] 通过设置这样的图像形成板208,可提高形成眼底图像和断层图像的图像数据的处理的处理速度。 [0192] plate 208 is formed by providing such an image forming process can increase the speed of processing image data of the tomographic image and the fundus image.

[0193] 通信接口209进行以下处理:将来自微处理器201的控制信号发送到眼底相机单元IA或OCT单元150。 [0193] The communication interface 209 performs the following process: a control signal sent from the microprocessor 201 to the fundus camera unit or the OCT unit 150 IA. 另外,通信接口209进行以下处理:接收来自眼底相机单元IA的摄像装置10、12的图像信号,或来自OCT单元150的(XD184的检测信号,输入到图像形成板208。此时,通信接口209进行动作,以将来自摄像装置10、12的图像信号输入到眼底图像形成板208a,并将来自(XD184的检测信号输入到OCT图像形成板208b。 Further, the communication interface 209 performs the following process: an imaging means receiving from the fundus camera unit 10, 12 an image signal IA, or a detection signal (XD184 from the OCT unit 150, and input to the image forming board 208. At this time, the communication interface 209 operates, the image signal from the imaging means 10, 12 is input to the fundus image forming board 208a, and from (XD184 detection signal is input to the OCT image forming board 208b.

[0194] 而且,当运算控制装置200连接于LAN (Local Area Network,局域网)或互联网等网络时,在通信接口209中可以具备局域网卡等网络适配器(network adapter)或调制解调器(modem)等通信设备,并能够经过该网络而进行数据通信。 [0194] Further, when the arithmetic and control unit 200 is connected to other LAN (Local Area Network, LAN) or the Internet network, communication interface 209 may include a LAN card, a network adapter (network adapter) or modem (Modem) like a communication device and can perform data communication through the network. 此时,可以在此网络上设置用于存储控制程序20½的服务器,并且将运算控制装置200构成为该服务器的客户终端, 借此可以使眼底观察装置1执行本实施形态的相关动作。 In this case, this may be provided on a network server for storing control programs of 20½, and the arithmetic control device 200 for client terminal of the server, whereby the fundus oculi observation device 1 can perform an operation related to the present embodiment. [0195][控制系统的结构] [0195] [Control System]

[0196] 接着,参照图5-7,说明眼底观察装置1的控制系统的结构。 [0196] Next, with reference to Figures 5-7, the configuration of the control system of the fundus observation device 1.

[0197](控制部) [0197] (control unit)

[0198] 眼底观察装置1的控制系统是以图5所示的运算控制装置200的控制部210为中心而构成的。 [0198] The control system of the fundus oculi observation device 1 is the control unit of the operation control apparatus shown in FIG. 5 210 200 as a center thereof. 控制部210包含微处理器201、RAM202、R0M203、硬盘驱动器204(控制程序204a)、通信接口209而构成。 The control unit 210 includes a microprocessor 201, RAM202, R0M203, hard disk drive 204 (control program 204a), a communication interface 209 configured.

[0199] 控制部210通过根据控制程序20½而动作的微处理器201,执行所述各种控制处理。 [0199] The control unit 210 according to various control processes by the microprocessor 201 and the control program 20½ operation is performed. 特别是关于眼底相机单元1A,控制部210执行镜片驱动机构Ml、242的控制,从而变更检流计镜141A、141B的位置,以及执行IXD140的内部固视标的显示动作的控制等。 Particularly with regard to the retinal camera unit. 1A, the control unit 210 executes the lens driving mechanism of Ml, control 242, thereby the galvanometer mirror 141A is changed, the position 141B, and the internal fixation target IXD140 performing display control operation and the like.

[0200] 而且,关于OCT单元150,控制部210进行低相干光源160和(XD184的控制,使密度滤镜173旋转的密度滤镜驱动机构244的控制,使参照镜片174在参照光LR的行进方向上移动的参照镜片驱动机构M3的控制等。 [0200] Further, on OCT unit 150, the control unit 210 controls the low coherence light source 160 and (XD184 of the density filter drive mechanism 173 controls the rotation density filter 244, the lens 174 of the reference light LR travels in the reference controlling the lens driving mechanism M3 with reference to the direction of movement.

[0201] 而且,控制部210执行如下的控制:将由眼底观察装置1所拍摄的两种图像,即,通过眼底相机单元IA所获得的眼底Ef表面的二维图像(眼底图像Ef)、以及基于由OCT单元150所获得的检测信号而形成的眼底Ef的断层图像,显示在用户接口(UI) 240的显示部MOA上。 [0201] Further, the control unit 210 executes the following controls: two kinds of images captured by a fundus observation device, i.e., two-dimensional image of the surface of the fundus oculi Ef obtained by the retinal camera unit IA (fundus image Ef), and based on tomographic image of the fundus Ef by the detection signal obtained by OCT unit 150 is formed, the display on the display unit MOA (UI) 240 in the user interface. 这些图像可分别在显示器204A上显示,也可以同时排列显示。 These images may be respectively displayed on the display 204A, may be arranged and displayed simultaneously. 另外,控制部210 的详细结构将根据图7在后文中叙述。 Further, the detailed configuration of the control unit 210 will be described later in accordance with FIG.

[0202](图像形成部) [0202] (image forming portion)

[0203] 图像形成部220进行根据来自眼底相机单元IA的摄像装置10、12的图像信号来形成眼底图像的图像数据的处理,以及根据来自OCT单元150的(XD184的检测信号来形成眼底Ef的断层图像的图像数据的处理。图像形成部220为包含图像形成板208和通信接口209等的结构。另外,本说明书中,也有将“图像”和与之对应的“图像数据”视作相同的情况。 [0203] The image forming section 220 performs processing of image data to form a fundus image from the image signal from the image pickup apparatus of the retinal camera unit 10, 12 IA, and forming the fundus oculi Ef based on the detection signal (XD184 from the OCT unit 150 processing the image data of the tomographic image. the image forming unit 220 to the image forming structure comprises a communication interface 209 and the plate 208 and the like. in the present specification, there are the "image" and the corresponding "image data" regarded as the same Happening.

[0204] 另外,用以取得眼底Ef的断层图像的眼底相机单元IA的各部、OCT单元150、图像形成部220 (OCT图像形成板208b)、以及图像处理部230构成形成眼底Ef的断层图像的“图像形成元件”的一例。 [0204] Further, IA retinal camera unit for obtaining a tomographic image of the fundus oculi Ef departments, the OCT unit 150, the image forming section 220 (OCT image forming board 208b), and an image processing section 230 is configured to form a tomographic image of the fundus oculi Ef "image forming element" is an example. 另外,本实施形态中的图像形成元件包含用以取得眼底Ef表面的二维图像的眼底相机单元IA的各部分、图像形成部220(眼底图像形成板208a)。 In the present embodiment, the image forming portions IA element comprises a retinal camera unit for obtaining a two-dimensional image of the surface of the fundus oculi Ef, the image forming section 220 (fundus image forming board 208a).

[0205](图像处理部) [0205] (image processing unit)

[0206] 图像处理部230对由图像形成部220形成的图像的图像数据实施各种图像处理。 Image data [0206] The image processing unit 230 of the image by the image forming portion 220 is formed of various image processing. 例如,图像处理部230进行如下的处理:根据基于来自OCT单元150的检测信号的断层图像,来形成眼底Ef的三维图像的图像数据的处理,或图像的亮度校正和色散校正等各种校 For example, the image processing unit 230 performs the following process: a tomographic image based on the detection signal from the OCT unit 150 to form a three-dimensional image processing of image data of the fundus oculi Ef based, or brightness correction and dispersion correction of images, and other school

正处理等。 It is processed and so on.

[0207] 另外,所谓的三维图像的图像数据是对三维排列的多个立体像素(voxel)分别赋予像素值而形成的图像数据,也称为立体数据(volumn data)或立体像素数据等等。 [0207] Further, the image data of a so-called three-dimensional image is a plurality of voxels (a voxel) of the three-dimensional arrangement is formed respectively assigned to pixel values ​​of the image data, also called three-dimensional data (volumn data) or the voxel data or the like. 在显示基于立体数据的图像时,图像处理部230对此立体数据进行绘制(rendering)(立体绘制或MIP (Maximum IntensityProjection :最大值投影)等),以形成从确定的视线方向观看时的仿真三维图像的图像数据。 In the drawing display (Rendering) (perspective drawing or MIP (Maximum IntensityProjection: maximum intensity projection), etc.) based on the stereo image data, which the stereoscopic image data processing section 230, to form a three-dimensional simulation when viewed from the view direction is determined image data of the image. 基于此图像数据的仿真三维图像则显示在显示部MOA中。 Simulated three-dimensional image based on this image data is displayed on the display unit in the MOA.

[0208] 而且,图像处理部230进行如下的处理:求出断层图像中所含的眼底Ef的各种层位置。 [0208] Further, the image processing unit 230 performs the following process: obtaining the position of the various layers of the fundus oculi Ef included in tomographic images. 在此,所谓层位置是指一种信息,该信息表示相当于眼底Ef的预定层的断层图像上的位置、或相当于邻接的层边界的断层图像上的位置等断层图像上的眼底Ef的预定层的位置。 Here, the term refers to a layer position information which indicates a position on the tomographic image corresponding to a predetermined layer of the fundus oculi Ef, corresponding to the fundus oculi Ef or a tomographic image on the position and the like on the tomographic image of the boundary layer adjacent position of a predetermined layer. 另外,图像处理部230根据所求出的层位置来运算层的厚度。 Further, the image processing unit 230 based on the calculated position of the layer thickness of the layer is calculated. 这些处理将在图7的说明中加以详述。 These processes will be described in detail in the description of FIG. 7.

[0209] 图像处理部230构成为包含微处理器201、RAM 202、ROM 203、硬盘驱动器204(控制程序204a)等。 [0209] The image processing unit 230 is configured to include a microprocessor 201, RAM 202, ROM 203, hard disk drive 204 (control program 204a) and the like.

[0210](用户接口) [0210] (user interface)

[0211] 用户接口(User hterface,UI) 240设有显示部MOA和操作部MOB。 [0211] User Interface (User hterface, UI) 240 is provided with a display portion and the operation portion MOA MOB. 显示部MOA 由显示器207等显示装置构成。 MOA display unit 207 displayed by the display apparatus. 操作部MOB由键盘205和鼠标206等输入装置和操作装置构成。 The operation unit and the operating unit MOB means of a keyboard 205 and a mouse 206 and the like constituting the input.

[0212](操作面板) [0212] (operation panel)

[0213] 对眼底相机单元IA的操作面板3a进行说明。 [0213] The operation panel 3a of the retinal camera unit IA is described. 例如,如图15所示,此操作面板3a 是配设在眼底相机单元IA的架台3上。 For example, as shown in Figure 15, this operation panel 3a is provided on the fundus camera unit of the gantry 3 IA.

[0214] 本实施例的操作面板3a和在背景技术段落中所说明的先前结构不同,其设置有: 为了取得眼底图像Ef而用于操作指示的操作部;为了取得眼底Ef的断层图像而用于操作指示的操作部(先前结构只设有前者的操作部)。 [0214] The operation panel 3a in the present embodiment and the background art described in the previous paragraph different structures, which is provided with: in order to obtain the fundus image Ef and an operation portion operating instructions; in order to obtain a tomographic image of the fundus oculi Ef with operation instruction to an operation portion (operation portion provided with only the previous structure of the former).

[0215] 本实施例中,通过设置这种操作面板3a,可以按照和操作先前的眼底相机时相同的要领,进行用以取得眼底图像Ef的操作和用以取得断层图像的操作。 [0215] In this embodiment, by providing such an operation panel 3a, the same operations and can follow a previous essentials fundus camera performs operation for obtaining a fundus image Ef and for obtaining tomographic images of the operation.

[0216] 例如,如图6所示,在操作面板3a中,设置有菜单键301、裂像(split)键302、拍摄光量键303、观察光量键304、颚托键305、摄影键306、变焦键307、图像切换键308、固视标切换键309、固视标位置调整键310、固视标尺寸切换键311以及模式切换旋钮312。 [0216] For example, as shown in FIG. 6, the operation panel 3a is provided with a menu key 301, the split image (Split) key 302, the photographing light amount key 303, observation light amount of the key 304, the chin rest button 305, shooting key 306, a zoom key 307, the image switch button 308, the fixation target switch button 309, a fixation target position adjusting button 310, the fixation target size switching button 311 and a mode switching knob 312.

[0217] 菜单键301是一种键,其用来操作以显示用户为了选择指定各种菜单(拍摄眼底Ef表面二维图像或断层图像等时的拍摄菜单,为了进行各种设定输入的设定菜单等)的预定菜单画面。 [0217] Menu key 301 is a key, which is used to display the shooting operation menu in order to select various menus specified (two-dimensional image capturing surface of the fundus oculi Ef or a tomographic image or the like when the user, in order to perform various setting inputs provided set menus, etc.) of a predetermined menu screen.

[0218] 当操作此菜单键301时,其操作信号被输入到控制部210。 [0218] When operating the menu key 301, the operation signal is inputted to the control unit 210. 控制部210对应于此操作信号的输入,使菜单画面显示在触摸屏11或显示部MOA上。 The control unit 210 corresponds to the operation signal input thereto, so that a menu screen displayed on the touch screen 11 or the display unit MOA. 另外,也可以在眼底相机单元IA中设置控制部(图中未示),并由该控制部将菜单画面显示在触摸屏11上。 Further, the control unit may be provided (not shown) in the fundus camera unit IA, the control unit by the menu screen 11 displayed on the touch screen.

[0219] 裂像(split)键302是用于切换对焦用的裂像亮线(例如,参照日本专利特开平9-66031等。也被称为裂像视标或裂像标记等)的点亮和熄灭而进行操作的键。 [0219] split image (Split) key 302 is a switch for the focusing of the split bright line image (e.g., see Japanese Patent Laid-Open 9-66031, etc. is also referred to as split or crack optotype image marks, etc.) point turned on and off to perform a key operation. 另外,用来使该裂像亮线投影到受检眼E的结构(裂像亮线投影部)例如是置放在眼底相机单元IA 内(图1中省略)。 Further, for making the split bright line projection image to the structure of the examinee's eye E (split bright line projection part like) is placed, for example, in the retinal camera unit IA (FIG. 1 are omitted).

[0220] 当操作此裂像键302时,其操作信号被输入到控制部210(或眼底相机单元IA内的所述控制部,以下相同)。 [0220] When the operating button 302 is split image of this, the operation signal is inputted to the control unit 210 (or the control unit in the fundus camera unit IA, hereinafter the same). 控制部210对应于该操作信号的输入,控制裂像亮线投影部,使裂像亮线投影到受检眼E。 The control unit 210 of the operation corresponding to the input signal, the control split bright line projection part like the split bright line image projected onto the examinee's eye E.

[0221] 拍摄光量键303是一种键,其用来操作以根据受检眼E的状态(例如水晶体的浊度等)等来调整拍摄光源103的输出光量(拍摄光量)。 [0221] photographing light amount key 303 is a key, which is used to operate the light output according to the state of the examinee's eye E (e.g., crystalline haze and the like) and the like to adjust the imaging light source 103 (photographing light amount). 在该拍摄光量键303中,例如,设置着用来增加拍摄光量的拍摄光量增加键“ + ”、用来减少拍摄光量的拍摄光量减少键“_”、 及用来将拍摄光量设定为预定的初始值(内设值)的复位键(中央按钮)。 In the imaging light amount key 303, for example, is provided with to increase imaging light amount photographing light amount increasing key "+", to reduce imaging photographing light amount of light amount reduction key "_", and for the shooting light amount is set to a predetermined initial value (Default values) reset button (center button).

[0222] 当操作拍摄光量键303的其中一个时,其操作信号被输入到控制部210。 [0222] When one of the operating key 303 of the imaging light amount, the operation signal is inputted to the control unit 210. 控制部210对应于该输入的操作信号,控制拍摄光源103,调整拍摄光量。 The control unit 210 corresponding to the operation of the input signal, the control imaging light source 103 to adjust the photographing light amount. [0223] 观察光量键304是一种键,其用来操作以调整观察光源101的输出光量(观察光量)。 [0223] observation light amount key 304 is a key, which is used to operate the output light amount (observation light amount) of the observation light source 101 to adjust. 在该观察光量键304中,例如,设置着用来增加观察光量的观察光量增加键“ + ”、及用来减少观察光量的拍摄光量减少键“_”。 In the observation light volume key 304, for example, is provided for increasing the observation light amount of the observation light amount increasing key "+", and to reduce the amount of imaging light observation light amount reduction key "_."

[0224] 当操作观察光量键304的其中一个时,其操作信号被输入到控制部210。 [0224] When the operation amount of the observation light in which a key 304, the operation signal is inputted to the control unit 210. 控制部210对应于所输入的操作信号,控制该观察光源101,以调整观察光量。 The control unit 210 corresponding to the operation signal input, controls the observation light source 101 to adjust the observation light amount.

[0225] 颚托键305是让图15所示颚托6的位置进行移动的键。 [0225] button 305 is to make the chin rest 15 illustrated in FIG. 6 the position of the jaw holder move key. 在颚托键305中,例如, 设置着使颚托6向上方移动的向上移动键(向上的三角形)、及使颚托6向下方移动的向下移动键(向下的三角形)。 In the chin rest key 305, e.g., arranged so that the jaw holder 6 upward movement upward movement key (upward triangles), and that the jaw holder 6 is moved downward to the downward moving key (downward triangles).

[0226] 当操作颚托键305的其中一个时,其操作信号被输入到控制部210。 [0226] When one of the operation keys 305 of the chin rest, the operation signal is inputted to the control unit 210. 控制部210对应于所输入的操作信号,控制颚托移动机构(图中未示),使颚托6向上方或下方移动。 The control unit 210 corresponds to the inputted operation signal controls a jaw holder movement mechanism (not shown) that moves the jaw holder 6 upward or downward.

[0227] 拍摄键306是一种键,作为触发键(trigger switch)而使用,用来取得眼底Ef的表面的二维图像或眼底Ef的断层图像。 [0227] photographing key 306 is a key, as a trigger button (trigger switch) is used for obtaining two-dimensional image of the fundus oculi Ef or a tomographic image of the surface of the fundus oculi Ef.

[0228] 当拍摄二维图像的菜单被选择时,若操作拍摄键306,则接受其操作信号的控制部210控制拍摄光源103而使拍摄照明光输出,并且根据从检测该眼底反射光的摄像装置10 所输出的图像信号,使眼底Ef的表面的二维图像显示在显示部MOA或触摸屏11上。 [0228] When the two-dimensional image photographing menu is selected, when the photographing operation key 306, the operation of which receives a control signal of the control unit 210 capturing the imaging light source 103 outputs the illumination light, and based on the fundus reflection light from the detection of the imaging the image signal output from the apparatus 10, so that the two-dimensional image of the surface of the fundus oculi Ef is displayed on the display unit 11 or touch screen MOA.

[0229] 另一方面,当取得断层图像的菜单被选择时,若操作拍摄键306,则接受其操作信号的控制部210控制低相干光源160而输出低相干光L0,并控制检流计镜141A、141B而使信号光LS进行扫描,且根据由检测干涉光LC的CCD184所输出的检测信号,使图像形成部220(以及图像处理部230)所形成的眼底Ef的断层图像显示在显示部MOA或触摸屏11 上。 [0229] On the other hand, when the tomographic image is acquired menu is selected, when the photographing operation key 306, a control unit which accepts the operation signal controls the low coherence light source 210 and 160 output low-coherence light L0, and controls the galvanometer mirror 141A, 141B to scan the signal light LS, and a detection signal detected by the interference light LC is outputted CCD184 the 220 (and an image processing section 230) of the tomographic image of the fundus oculi Ef formed by the image forming section displayed on the display unit MOA or touch screen 11.

[0230] 变焦(zoom)键307是一种键,其用来操作以变更眼底Ef拍摄时的视角(变焦倍率)。 [0230] Zoom (Zoom) key 307 is a key, which is used to operate to change the angle of view (zoom magnification) at the time of photographing the fundus oculi Ef. 在每次操作此变焦键307时,例如交替地设定成摄影视角为45度和22. 5度。 Each time the zoom key 307 operations, e.g. alternately set to a photographing view angle of 45 degrees and 22.5 degrees.

[0231] 当操作此变焦键307时,接受其操作信号的控制部210控制倍率可变透镜驱动机构(图中未示),使倍率可变透镜1¾在光轴方向上移动,以变更拍摄视角。 [0231] When 307, receiving section 210 controls the operation of the gain control signal variable lens driving mechanism (not shown), so the magnification variable lens 1¾ moved in the optical axis direction to change the operation of the zoom key shooting angle .

[0232] 图像切换键308是一种用来操作以使显示图像切换的键。 [0232] Image 308 is a switch button for operating the key so that the display image switching. 当眼底观察图像(基于来自摄像装置12的图像信号的眼底Ef的表面的二维图像)显示在显示部MOA或触摸屏11上时,若操作图像切换键308,则接受其操作信号的控制部210使眼底Ef的断层图像显示在显示部MOA或触摸屏11上。 When the fundus observation image (based on the surface of the fundus oculi Ef of the image signal from the imaging device 12 is a two-dimensional image) is displayed on the display unit MOA or touch screen 11, when the operating image switching button 308, the acceptance control unit the operation signal 210 Ef fundus tomographic image is displayed on the display unit 11 or touch screen MOA.

[0233] 另一方面,当眼底的断层图像显示在显示部MOA或触摸屏11上时,若操作该图像切换键308,则接受其操作信号的控制部210使眼底观察图像显示在显示部MOA或触摸屏11上。 [0233] On the other hand, when the tomographic image of the fundus is displayed on the display unit 11 MOA or a touch screen, when the image switching operation of the key 308, the control unit receiving the operation signal 210 causes a fundus observation image displayed on the display unit or MOA the touch screen 11.

[0234] 固视标切换键309是用来操作以对利用IXD的内部固视标的显示位置(即在眼底Ef的内部固视标的投影位置)进行切换的键。 [0234] fixation target switch key 309 is used to operate the internal fixation target on the use IXD display position (i.e., within the fundus oculi Ef fixation target projection position) of the key switch. 通过操作此固视标切换键309,例如,使内部固视标的显示位置在“用来取得眼底中心的周边区域的图像的固视位置(眼底中心拍摄用固视位置)”、“用来取得黄斑的周边区域图像的固视位置(黄斑拍摄用固视位置)”、及“用来取得视神经乳头的周边区域图像的固视位置(视神经乳头拍摄用固视位置)”之间做巡回切换。 By operating this fixation target switching key 309, e.g., so that the display position of the internal fixation target in the "fixation position for acquiring the image of the fundus of the peripheral region of the center (center of the captured fundus with fixation position)", "is used to obtain the position of the image outside the fixation region of macula lutea (macular taken with the fixation position) ", and" fixation position for acquiring images of the peripheral region of optic papilla (optic papilla imaging position by fixation) do "between circuit switching.

[0235] 控制部210对应于来自固视标切换键309的操作信号,使内部固视标显示在LCD140的显示面上的相异位置。 [0235] the control unit 210 from the fixation target corresponding to the operation signal from the key switch 309, and display the internal fixation target in different positions on the display surface of LCD140. 另外,对应于所述三个固视位置的内部固视标的显示位置,例如,可根据临床数据预先设定,或也可以针对每个受检眼E(眼底Ef的图像)而事先设定。 Further, corresponding to the three fixation positions of the display position of the internal fixation target, for example, based on clinical data may be set in advance, or may be set in advance for each of the examinee's eye E (image of the fundus oculi Ef).

[0236] 固视标位置调整键310是用来操作以调整内部固视标的显示位置的键。 [0236] fixation target position adjusting operation key 310 is used to adjust the displayed internal fixation target key position. 在此固视标位置调整键310中,例如,设置着用来使内部固视标的显示位置向上方移动的上方移动键、用来使之向下方移动的下方移动键、用来使之向左移动的左方移动键、用来使之向右移动的右方移动键、及用来使之移动到预定的初始位置(内设(default)位置)的复位(reset)键。 The fixation target position adjusting button 310, for example, used to set the internal fixation target displayed above the shift key move in the upward position, to move downward so that downward movement key, to move it to the left the left movement key, to move to the right so that the right moving key, and is used to move it to a predetermined initial position (site (default) position) reset (rESET) key.

[0237] 控制部210当接受到来自固视标位置调整键310中的任一键的操作信号时,对应于该操作信号而控制IXD140,借此使内部固视标的显示位置移动。 [0237] When the control unit 210 receives the operation signal from the fixation target position adjusting key 310 is a key, corresponding to the operation signal controls IXD140, whereby the display position of the internal fixation target movement.

[0238] 固视标尺寸切换键311是用来操作以变更内部固视标尺寸的键。 [0238] fixation target size switching button 311 is used to operate to change the size of the internal fixation target key. 当操作此固视标尺寸切换键311时,接受其操作信号的控制部210变更在LCD140上显示的内部固视标的显示尺寸。 When operating this fixation target size switching button 311, the operation accepting unit 210 a control signal to change the internal fixation target displayed on the display LCD140 size. 内部固视标的显示尺寸例如在“一般尺寸”和“加大尺寸”之间交替切换。 Display size of the internal fixation target, for example, between "general dimension" and "oversized" alternately switched. 借此, 变更投影在眼底Ef的固视标投影像的尺寸。 Accordingly, the change in size of the projection of the fundus oculi Ef fixation mark projection image. 控制部210当接受到来自固视标尺寸切换键311的操作信号时,根据该操作信号而控制LCD140,借此变更内部固视标的显示尺寸。 When the control unit 210 receives the time from the fixation target size switching button 311 of the operation signal, the operation signal controls the LCD 140, thereby changing the display size of the internal fixation target.

[0239] 模式切换旋钮(knob) 312是一种用来旋转操作以选择各种摄影模式(对眼底Ef 的二维图像进行拍摄的眼底拍摄模式、进行信号光LS的B扫描的B扫描模式、使信号光LS 进行三维扫描的三维扫描模式等)的旋钮。 [0239] Mode switching knob (knob) 312 for a rotational operation to select various photographing mode (two-dimensional image of the fundus Ef is photographed fundus photographing mode, B-mode scanning light LS B-scan signal, knob of the signal light LS three-dimensionally scanning a three-dimensional scan mode, etc.). 另外,此模式切换旋钮312也可以选择再生模式,其用以对取得的眼底Ef的二维图像或断层图像进行再生显示。 In addition, this mode switching knob 312 may be selected reproduction mode, for which the two-dimensional image or tomographic image of the fundus Ef acquired reproduced and displayed. 而且,也可以选择拍摄模式,用来控制使信号光LS扫描后立刻进行眼底拍摄。 Further, the shooting mode may be selected for controlling the signal light LS scan performed immediately after photographing the fundus. 用来使眼底观察装置1执行和所述各模式对应的动作的装置各部的控制是由控制部210执行。 Execution means for causing the fundus observation device 1 and each portion of the pattern corresponding to each of the operation control is executed by the control unit 210.

[0240] 以下,分别说明利用控制部210所进行的信号光LS的扫描的控制形态,以及利用图像形成部220和图像处理部230对来自OCT单元150的检测信号的处理状态。 [0240] Hereinafter, the control mode respectively illustrate scanning of the signal light LS is performed by the control unit 210, and the processing state 230 pairs of detection signals by the image forming section 150 and the image processing unit 220 from the OCT unit. 另外,对来自眼底相机单元IA的图像信号的图像形成部220等的处理,和先前的处理相同,故省略说明。 Further, processing of the image forming unit 220 image signal from the fundus camera unit IA, the same as the processing previously, the description thereof will be omitted.

[0241][关于信号光的扫描] [0241] [on the scanning signal light]

[0242] 信号光LS的扫描如上所述,是通过变更眼底相机单元IA的扫描单元141的检流计镜141A、141B的位置(反射面的朝向)而进行。 [0242] As described above the signal light LS is scanned, the scanning unit by changing the fundus camera unit IA is a galvanometer mirror 141A 141 and 141B of the position (toward the reflective surface) is performed. 控制部210分别控制镜片驱动机构Ml、 242,以此分别变更检流计镜141A、141B的反射面的朝向,由此在眼底Ef上扫描信号光LS 的照射位置。 The control unit 210 controls a lens driving mechanism, respectively Ml, 242, respectively, in order to change a galvanometer mirror 141A, 141B toward the reflection surface, whereby the irradiation position of the scanning of the signal light LS on the fundus Ef.

[0243] 当变更检流计镜141A的反射面的朝向时,在眼底Ef的水平方向上(图1的χ方向)扫描信号光LS。 [0243] When changing the direction of the reflecting surface of the galvanometer mirrors 141A and, in the horizontal direction of the fundus oculi Ef ([chi] direction in FIG. 1) scans the signal light LS. 另一方面,当变更检流计镜141Β的反射面的朝向时,在眼底Ef的垂直方向(图1的y方向)上扫描信号光LS。 On the other hand, when the change of the reflection surface toward the galvanometer mirror 141Β meter, and the fundus Ef in the vertical direction (y direction in FIG. 1) scans the signal light LS. 而且,同时变更检流计镜141A、141B两者的反射面的朝向,以此可以在χ方向和y方向的合成方向上扫描信号光LS。 Further, while changing a galvanometer mirror 141A, 141B toward the reflection surfaces of both the order may scan the signal light LS in the composite direction χ and y directions. 即,通过控制这两个检流计镜141A、141B,可以在xy平面上的任意方向上扫描信号光LS。 That is, by controlling these two Galvanometer mirrors 141A, 141B, the signal light LS may be scanned in an arbitrary direction in the plane xy.

[0244] 图8表示用以形成眼底Ef的图像的信号光LS的扫描形态的一例。 [0244] FIG. 8 shows one case to form a scanning signal light LS image the fundus oculi Ef is formed. 图8 (A)表示从信号光LS入射受检眼E的方向观察眼底Ef (也就是从图1的-ζ方向观察+ζ方向)时, 信号光LS的扫描形态的一例。 Figure 8 (A) shows a view from the direction of the fundus oculi Ef of the subject's eye E is incident light LS signal (i.e. observed from the + ζ direction -ζ direction in FIG. 1), one case of scanning the signal light LS to form. 而且,图8 (B)表示眼底Ef上的各扫描线上扫描点(进行图像计测的位置;信号光LS的照射位置)的排列形态的一例。 Further, FIG. 8 (B) represents each scanning line on the fundus Ef of the scanning spot (the image measurement position; irradiation position of the signal light LS) is an example of the array pattern.

[0245] 如图8㈧所示,在例如矩形的扫描区域R内扫描信号光LS。 [0245] As shown in, for example, within a rectangular scanning region R of the scanning signal light LS 8㈧ FIG. 在该扫描区域R内,在χ方向上设定有多条(m条)扫描线Rl〜Rm。 Within this scanning region R, setting (m bar) Rl~Rm plurality of scanning lines in the direction χ. 当沿着各扫描线Ri (i = 1〜m)扫描信号光LS时,产生干涉光LC的检测信号。 When along each scanning line Ri (i = 1~m) scanning the signal light LS, generates a detection signal of the interference light LC.

[0246] 在此,将各扫描线Ri的方向称为“主扫描方向”,将和该方向垂直的方向称为“副扫描方向”。 [0246] Here, the direction of each scanning line Ri is referred to as "main scanning direction", the direction and the vertical direction is referred to as the "sub-scanning direction." 因此,在主扫描方向上扫描信号光LS是通过变更检流计镜141A的反射面的朝向而进行,在副扫描方向上的扫描是通过变更检流计镜141B的反射面的朝向而进行。 Thus, the scanning signal light LS in the main scanning direction is performed by changing the facing reflective surface of the galvanometer mirror 141A, and scanning in the sub-scanning direction is performed by changing the galvanometer toward the reflective surface of the galvanomirror and 141B.

[0247] 在各扫描线Ri上,如图8(B)所示,预先设定有多个(η个)扫描点Ril_Rin。 [0247] On each scanning line Ri, as shown in FIG 8 (B), the previously set plurality of ([eta] a) scanning points Ril_Rin.

[0248] 为了执行图8所示的扫描,控制部210首先控制检流计镜141A、141B,将对眼底Ef 的信号光LS的入射目标设定为第1扫描线Rl上的扫描开始位置RS(扫描点Rll)。 [0248] In order to perform a scan shown in FIG. 8, the control unit 210 first controls the galvanometer mirrors 141A, 141B, will fundus oculi Ef of the signal light LS enters the destination to the scan start position RS on the first scanning line Rl (scanning point Rll). 接着, 控制部210控制低相干光源160,使低相干光LO闪光,并使信号光LS入射于扫描开始位置RS。 Next, the control unit 210 controls the low coherence light source 160, a low-coherence light LO flash, and the signal light LS entering the scan start position RS. (XD184接收该信号光LS的扫描开始位置RS上因眼底反射光而来的干涉光LC,并将检测信号输出至控制部210。 (Due to the fundus reflection light from the interference light LC and outputs a detection signal to the control unit 210 receives the scan start position RS XD184 of the signal light LS.

[0249] 接着,控制部210控制检流计镜141A,并在主扫描方向上扫描信号光LS,将该入射目标设定为扫描点R12,使低相干光LO闪光而使信号光LS入射到扫描点R12。 [0249] Next, the control unit 210 controls the galvanometer mirror 141A, and scanning the signal light LS in the main scanning direction and set the incident target of the scanning point R12, makes the low-coherence light LO flashing signal light LS incident scanning point R12. (XD184接收该信号光LS的扫描点R12上因眼底反射光而来的干涉光LC,并将检测信号输出至控制部210。 (Due to the fundus reflection light from the interference light LC and outputs a detection signal to the control unit 210 receives the signal light LS XD184 scanning spot R12.

[0250] 控制部210同样,一边将信号光LS的入射目标依次移动为扫描点R13、R14..... [0250] Also the control unit, while the incident target of the signal light LS sequentially moving the scanning spot 210 is R13, R14 .....

Rl (n-1)、Rln, 一边在各扫描点上使低相干光LO闪光,以此获取和各扫描点的干涉光LC相对应地从(XD184所输出的检测信号。 Rl (n-1), Rln, while in the low-coherence light LO flash each scanning point, and in order to obtain the interference light LC for each scanning point corresponding to the (detection signal outputted XD184.

[0251] 当第1扫描线Rl的最后的扫描点Rln上的计测结束时,控制部210同时控制检流计镜141A、141B,使信号光LS的入射目标沿着换线扫描r而移动到第2扫描线R2最初的扫描点R21为止。 [0251] Upon completion of the measurement on the last scanning spot Rl Rln first scan line, the control unit 210 while controlling the galvanometer mirror 141A, 141B, the incident target of the signal light LS is moved along a scan line changing r to the second scanning line R2 until the original scanning spot R21. 而且,对该第2扫描线R2的各扫描点R2j (j = 1-n)进行所述计测,以此分别获取对应于各扫描点R2j的检测信号。 Also, each scanning point the second scanning line R2, R2j (j = 1-n) for the measurement, in order to obtain respectively corresponding to each scanning point detection signal R2 j.

[0252] 同样,分别对第3扫描线R3.....第m-1扫描线R(m_l)、第m扫描线Rm进行计测, [0252] Similarly, each of the third scanning line R3 ..... m-1 the first scanning line R (m_l), for the m-th scanning line Rm is measured,

从而获取对应于各扫描点的检测信号。 Thereby acquiring corresponding to each of the scanning spot detection signals. 另外,扫描线Rm上的符号RE是对应于扫描点Rmn 的扫描结束位置。 Furthermore, the symbol RE on a scanning line Rm is a scan of scanning point Rmn correspond to the end position.

[0253] 以此,控制部210获取对应于扫描区域R内的mXη个扫描点Rij (i = 1〜m,j = 1〜η)的mXn个检测信号。 [0253] In this, the control unit 210 acquires corresponding to the scanning region R of mXη scanning points Rij (i = 1~m, j = 1~η) mXn the detection signals. 以下,将对应于扫描点Ri j的检测信号表示为Di j。 Hereinafter, the scanning point corresponding to the detection signal Ri j is represented as Di j.

[0254] 如上所述的扫描点的移动和低相干光LO的输出的连动控制,例如,可以通过使控制信号相对于镜片驱动机构M1J42的发送时序(timing)、和控制信号(输出要求信号) 相对于低相干光源160的发送时序互相同步而实现。 Interlocking control [0254] the scanning spot moves as described above and the low-coherence light LO output, for example, by a lens driving control signal transmission means M1J42 timing (Timing) with respect to, and control signals (output request signal ) with respect to the low coherence light source 160 transmits a timing synchronized with each other is achieved.

[0255] 当控制部210如上所述使各检流计镜141A、141B动作时,存储有各扫描线Ri的位置或各扫描点Rij的位置(xy坐标系中的坐标),作为表示其动作内容的信息。 [0255] When the control unit 210 as described above so that each of the galvanometer mirror 141A, 141B during operation, stores a position of each scanning line Ri or the position of each scanning point Rij (the coordinate in the xy coordinate system), as represented by its operation information content. 该存储内容(扫描点坐标信息)和先前同样用于图像形成处理中。 This stored content (scanning point coordinate information) and a previous image forming process for same.

[0256][关于图像处理] [0256] [Regarding Image Processing]

[0257] 以下,针对图像形成部220及图像形成处理部230的OCT图像(眼底Ef的断层图像)有关的处理,说明其中之一例。 [0257] Here, the processing relating to OCT images (tomographic images of the fundus oculi Ef) 230 is formed for the image processing section 220 and an image forming section, an example of which.

[0258] 图像形成部220执行沿着各扫描线Ri (主扫描方向)的眼底Ef的断层图像形成处理。 [0258] The image forming section 220 performs a tomographic image formed along each scanning process line Ri (main scanning direction) of the fundus oculi Ef. 而且,图像处理部230进行基于图像形成部220形成的断层图像的眼底Ef的三维图像的形成处理等。 Further, the image processing unit 230 performs three-dimensional image formation process of a tomographic image of the fundus oculi Ef is formed by the image forming portion 220 and the like based. [0259] 图像形成部220的断层图像的形成处理和先前同样,包含两阶段的运算处理。 [0259] The image forming portion forming process 220 of the tomographic image and the previous similar, comprising a two-stage arithmetic processing. 在第1阶段的运算处理中,根据对应于各扫描点Rij的检测信号Dij,形成在该扫描点Rij的眼底Ef的深度方向(图1所示ζ方向)的图像。 In the first stage of arithmetic processing in accordance with each scanning point corresponding to the detection signal Dij of Rij, the image of the fundus Ef is formed of the scanning point Rij depth direction ([zeta] direction shown in FIG. 1).

[0260] 图9表示由图像形成部220所形成的断层图像(群)的形态。 [0260] FIG. 9 shows a form of a tomographic image formed by the image forming section 220 (group) in. 在第2阶段的运算处理中,对于各扫描线Ri,根据其上的η个扫描点Ril〜Rin上的深度方向的图像,形成沿着该扫描线Ri的眼底Ef的断层图像Gi。 In the second stage arithmetic process, for each scanning line Ri, the image in the depth direction of the scanning spot Ril~Rin η thereon, forming a tomographic image Gi of the fundus oculi Ef along the scanning line Ri. 此时,图像形成部220参照各扫描点Ril-Rin的位置信息(所述扫描点坐标信息),决定各扫描点Ril〜Rin的排列及间隔,并形成该扫描线Ri。 At this time, the position information of the scanning spot 220 with reference to the image forming portion of Ril-Rin (the scanning point coordinate information) of each scanning point Ril~Rin determined arrangement and spacing, and forming the scanning line Ri.

[0261] 经过以上的处理,可获得副扫描方向(y方向)上不同位置上的m个断层图像Gl〜 Gm0 [0261] Through the above process, is obtained sub scanning direction (y direction) of m number of tomographic images at different positions on Gl~ Gm0

[0262] 接着,说明图像处理部230的眼底Ef的三维图像的形成处理。 [0262] Next, a process of forming a three-dimensional image of the fundus Ef of an image processing unit 230. 眼底Ef的三维图像是根据通过所述运算处理所获得的m个断层图像Gl〜Gm而形成。 Three-dimensional image of the fundus oculi Ef is formed by the arithmetic process according to the obtained tomographic images m Gl~Gm. 图像处理部230进行在邻接的断层图像Gi、G(i+l)之间内插图像的众所周知的内插处理等,从而形成眼底Ef的 The image processing unit 230 performs a tomographic image Gi of the adjacent, between the interpolation images G (i + l) known interpolation processing and the like, thereby forming the fundus oculi Ef

三维图像。 Three-dimensional image.

[0263] 此时,图像处理部230参照各扫描线Ri的位置信息而决定各扫描线Ri的排列及间隔,从而形成其三维图像。 [0263] In this case, the image processing unit 230 with reference to the position information of each scanning line Ri is determined and the arrangement intervals of each scanning line Ri to form a three-dimensional image. 该三维图像中,基于各扫描点Rij的位置信息(所述扫描点坐标信息)和深度方向的图像的ζ坐标,设定三维坐标系(x、y、z)。 The three-dimensional image, based ζ coordinate position information (the scanning point coordinate information) of each scanning point Rij and the image in the depth direction, setting a three-dimensional coordinate system (x, y, z).

[0264] 而且,图像处理部230根据该三维图像,可以形成主扫描方向(χ方向)以外的任意方向的截面上眼底Ef的断层图像。 Tomographic image of the fundus Ef on a cross section in an arbitrary direction [0264] Moreover, the image processing unit 230 based on the three-dimensional image can be formed in the main scanning direction (direction [chi]) outside. 当指定截面时,图像处理部230确定该指定截面上的各扫描点(及/或所内插的深度方向的图像)的位置,并从三维图像中提取各确定位置上深度方向的图像(及/或所内插的深度方向的图像),且将所提取的多个深度方向的图像进行排列,借此形成该指定截面上眼底Ef的断层图像。 When the specified section, the image processing unit 230 determines the position of each scanning point (and / or image in the depth direction is interpolated by) on the designated cross-section, and extracts an image in the depth direction of the respective determined positions on the three-dimensional image (and / within the image or the interpolated depth direction), and the depth direction of the plurality of images extracted are arranged, thereby forming a tomographic image of the fundus oculi Ef of the specified section.

[0265] 另外,图9所示的图像Gmj表示扫描线Rm上的扫描点Rmj上深度方向(ζ方向)的图像。 [0265] Furthermore, the image Gmj shown in FIG. 9 represents a scanning spot on the scanning line Rm Rmj image in the depth direction ([zeta] direction). 同样,可用“图像Gij”来表示在所述第1阶段的运算处理中所形成的、各扫描线Ri 上的各扫描点Rij上的深度方向的图像。 Similarly, the available "image Gij" to represent the image in the depth direction at each scanning point Rij on each scanning line Ri in the first phase formed in the arithmetic processing.

[0266][运算控制装置的详细结构] [0266] [Detailed configuration of the arithmetic control device]

[0267] 参照图7,说明运算控制装置200的详细结构。 [0267] Referring to FIG 7, a detailed configuration of the arithmetic control device 200. 在此,对运算控制装置200的控制部210以及图像处理部230特别进行详细说明。 Here, the detailed description of the image processing unit 210 and a control unit 230 particularly controls operation of the apparatus 200.

[0268](控制部) [0268] (control unit)

[0269] 在运算控制装置200的控制部210中,设置着主控制部211和存储部212。 [0269] In the control unit 210 of the arithmetic and control unit 200 is provided with a main control unit 211 and a storage unit 212. 主控制部211执行控制部210的所述各种控制处理。 The main control unit 211 performs control section 210 controls various processing. 另外,主控制部211执行在存储部212中存储数据的处理、以及读出存储部212中存储的数据的处理。 Further, the main processing unit 211 performs the control process 212 is stored in the data storage unit, and reads out the data stored in the storage unit 212.

[0270] 存储部212存储断层图像Gi (i = 1〜m)或眼底图像Ef等的图像。 [0270] storage unit 212 stores tomographic images Gi (i = 1~m) image of the fundus image Ef or the like. 另外,存储部212存储光学信息V。 Further, the storage unit 212 stores optical information V.

[0271] 光学信息V包括和受检眼E的眼球光学系统相关的信息。 [0271] The optical information V includes information on the optical system and the eye E of the examinee's eye related. 具体来说,光学信息V 中,包含受检眼E的角膜曲率(曲率半径)、屈光度(屈光力)、眼轴长度等的测定值。 Specifically, in the optical information V includes the measured value of the examinee's eye E, corneal curvature (radius of curvature), refractive power (refractive power), the axial length and the like. 在此, 作为屈光度的测定值,例如可以使用根据受检眼E的球面度的测定值“S”、散光度的测定值“C”所获得的值“S+C/2”。 Here, as the measurement value diopters, for example, may be used in accordance with the measured value of the examinee's eye E sphere of "S", the value of astigmatism measured value "C" acquired "S + C / 2". 另外,光学信息V包含角膜曲率、屈光度、眼轴长度等的眼球光学系统的特征参数中的至少一个的测定值即可。 Further, the optical information V characteristic parameters can comprise the measured value of the optical system of the eye corneal curvature, refractive power, axial length of at least one. 另外,这些参数中,对眼底观察装置1的计测影响最大的是角膜曲率。 Further, these parameters affect the measurement of the fundus observation device 1 is the maximum curvature of the cornea. 因此,光学信息V中含有角膜曲率的测定值则较为理想。 Thus, the measured value of corneal curvature contained in the optical information V is preferable.

[0272] 角膜曲率、屈光度或眼轴长度的测定值是利用和先前同样的眼科装置事先测定的。 [0272] corneal curvature, refractive power, or the measured value of the ocular axial length is measured in advance using a previous same ophthalmic device. 这些测定值例如由利用通信线路来和眼底观察装置1连接的电子绘图(Karte)服务器(图中未示)等取得。 These measured values ​​servers (not shown) or the like acquired by the communication line using the fundus oculi observation device and an electronic drawing connection (Karte) for example. 另外,也可以由检测者对操作部MOB进行操作,以输入测定值。 Further, the operation may be performed by the operation unit MOB examiner to input measured values. 而且,也可以利用运算控制装置200的驱动装置(图中未示)来读取并输入存储媒体中存储的测定值。 Further, the input may be read and the measured value stored in the storage medium by a drive means (not shown) of the arithmetic and control unit 200.

[0273] 另外,光学信息V也可以含有显示受检眼E内是否安装着眼内透镜的信息(眼内透镜信息)。 [0273] Further, the optical information V may contain information display whether the focus lens (intraocular lens information) is mounted within the examinee's eye E. 当安装了眼内透镜时,也可以将该眼内透镜的度数或颜色等信息记录为眼内透fefn 息。 When the installation of the intraocular lens, can be recorded in the intraocular lens or other color information for the degree of interest fefn intraocular lens.

[0274] 存储部212作为本发明的“存储元件”的一个例子而发挥作用。 [0274] As the storage unit 212 according to the present invention, an example of the "storage element" in the play. 存储部212例如可以包含硬盘驱动器204等存储装置而构成。 For example, the storage unit 212 may include a storage device such as a hard disk drive 204 is constituted.

[0275](图像处理部) [0275] (image processing unit)

[0276] 在图像处理部230中,设置着倍率运算部231和分析部232。 [0276] In the image processing section 230 is provided with the magnification operation part 231 and analyzing part 232. 倍率运算部231进行受检眼E的眼球光学系统的倍率运算,因此作为本发明的“运算元件”的一个例子而发挥作用。 Magnification operation unit 231 magnification of the optical system eye operation examinee's eye E, and therefore as an example of the "calculating device" of the present invention to function.

[0277] 另外,分析部232对断层图像Gi进行分析,因此作为本发明的“分析元件”的一个例子而发挥作用。 [0277] Further, the analysis unit 232 to analyze tomographic image Gi, so as an example of the "analysis device" of the present invention to function. 分析部232的分析对象处除了眼底的层厚度以外,另有层的缺损范围或肿瘤的尺寸或位置等。 Analysis at the object analysis unit 232 in addition to the layer thickness of the fundus, the range of defect size or position, or the like and another layer of tumors. 一般来说,分析对象是能够作为绝对尺寸或位置而进行评价的眼底的任意特征部位。 In general, any analyte capable of characteristic portions of the fundus evaluated as an absolute location or size. 该特征部位例如是用mm、mm2、mm3、μ m、μ m2、μ m3等维数来表现的。 This feature is, for example, the dimension of parts mm, mm2, mm3, μ m, μ m2, μ m3 like performance. 在分析部232中,设置着积分图像形成部233、定位部234、计测位置设定部235以及层厚计测部236。 In the analyzing portion 232, it is provided with an integral image forming unit 233, positioning unit 234, the measurement position setting part 235, and the layer thickness measuring section 236.

[0278](倍率运算部) [0278] (magnification operation part)

[0279] 倍率运算部231根据存储部212中存储的光学信息V,来运算受检眼E的眼球光学系统的倍率。 [0279] Magnification operation unit 231 The memory unit 212 stores optical information V, calculates the magnification of the optical system of the eye E of the examinee's eye. 如上所述,光学信息V中,记录着受检眼E的角膜曲率、屈光度、目艮轴长度的测定值或者眼内透镜信息。 As described above, the optical information V, the recorded subject eye E corneal curvature, refractive power, axial length of the measurement value Gen mesh information or an intraocular lens. 以下,说明倍率运算部231所实行的处理的一个例子。 Hereinafter, an example of processing operation unit 231 magnification implemented. 本实施形态中,求出考虑到受检眼E的倍率和拍摄光学系120的倍率两者所得的拍摄倍率。 In this embodiment, the magnification is determined taking into account the subject's eye E and the photographing optical system 120 obtained in both the magnification of photographing magnification.

[0280] 首先,倍率运算部231在屈光度为角膜顶点的测定值(角膜屈光力)时,视需要将此屈光度转换为瞳孔的屈光度(瞳孔屈光力)。 When [0280] First, the operation unit 231 magnification diopter measurement values ​​of the vertices of the cornea (corneal refractive power), as needed to convert this diopters diopters pupil (pupil refractive power). 该运算例如可以和先前同样地根据眼镜佩戴距离和从角膜顶点到入射瞳为止的距离来进行。 This operation can be, for example, and according to the same manner as previously spectacle wearer and the distance up to the entrance pupil from the corneal vertex distance is performed.

[0281] 其次,倍率运算部231运算物镜113的眼底图像的成像位置。 [0281] Next, the imaging position of the fundus image arithmetic operating unit 231, a magnification of the objective lens 113. 例如,该运算可以根据瞳孔屈光力、物镜113的焦距、从入射瞳到物镜113前侧焦点为止的距离,使用牛顿的运算式来进行。 For example, the calculation may pupil refractive power, a focal length of the objective lens 113, the distance from the entrance pupil of the front-side focal point of the objective lens 113 up, using Newton's equation for calculation.

[0282] 接着,倍率运算部231运算倍率可变透镜(聚焦透镜)124的拍摄倍率。 [0282] Next, a magnification ratio calculation unit 231 calculating the variable lens (focus lens) 124. The photographing magnification. 该运算例如可以通过如下方式来进行,即,针对拍摄倍率,求出表示物镜113成像位置的运算结果、 倍率可变透镜124的焦距、主点间距离、物像距离的关系的2次式。 This operation may be performed, for example, the following manner, i.e., for the photographing magnification, the calculation result is obtained showing the imaging position of the objective lens 113, the magnification of the variable focal length lens 124, the distance between the principal points, the relationship of Formula 2 was like distance.

[0283] 接着,倍率运算部231运算来自物镜113的射出角。 [0283] Next, operation unit 231 magnification operation from the emission angle of the objective lens 113. 例如可以根据拍摄倍率的运算结果、从物镜113的后侧主点到拍摄光圈121为止的距离、物镜113的焦距来进行该运算。 For example, according to the calculation result of the photographing magnification, from the rear side principal point of the objective lens 113 to the subject distance until the aperture 121, the focal length of the objective lens 113 to perform the calculation. 此时,以使像的检测面中像的高度达到预定值的方式来运算射出角。 At this time, the detection surface of the image height of the image in a predetermined manner emission angle value is calculated. 该预定值例如设为-0. Imm(负号表示从光轴向下(_y方向)使像形成)。 The predetermined value is set to, for example, -0. Imm (negative sign means downward from the optical axis (_y direction) so that the image is formed).

22[0284] 接着,倍率运算部231以使拍摄光圈121的光圈面中像的高度达到所述预定值的方式来运算入射到物镜113的入射角。 22 [0284] Next, magnification operation part 231 causes the imaging aperture diaphragm 121 reaches the height of the image plane in the manner of a predetermined value is calculated incidence angle of the objective lens 113. 例如可以根据来自物镜113的射出角的运算结果、 入射瞳和拍摄光圈121的角度倍率来进行该运算。 For example, the calculation may be performed based on the calculation result from the emission angle of the objective lens 113, the entrance pupil and the imaging diaphragm 121 angle magnification.

[0285] 接着,倍率运算部231运算受检眼E的角膜的后表面的曲率半径。 [0285] Next, the radius of curvature of the rear surface of the cornea of ​​the examinee's eye E 231 magnification arithmetic operation unit. 例如可以根据光学信息V中记录的角膜曲率(角膜前表面曲率)的测定值、角膜的前表面及后表面的曲率比来进行该运算。 For example, the measured value of corneal curvature (anterior corneal curvature) recorded in the optical information V, the curvature of the front and back surfaces of the cornea is the ratio calculation. 例如,该曲率比可以使用基于临床数据或模型眼等的标准值。 For example, the ratio of the curvature can use a standard value based on clinical data, or the like of the model eye. 另外,例如,当使用角膜用的OCT装置等来测定角膜的后表面的曲率(曲率半径)后,也可以使用该测定值来作为角膜后表面的曲率半径。 Further, for example, when the curvature (radius of curvature) of the rear surface of the cornea was measured using an OCT apparatus with the cornea and the like, may be used as the measured value of the radius of curvature of the rear surface of the cornea.

[0286] 接着,倍率运算部231运算远点和物体(角膜顶点)的距离。 [0286] Next, magnification operation part 231 and the far point calculation object (corneal vertex) distance. 例如可以根据角膜顶点的屈光度、眼镜佩戴距离来进行该运算。 The distance may be worn, for example, corneal vertex diopter, glasses for this calculation.

[0287] 接着,倍率运算部231运算从受检眼E的水晶体的后表面到视网膜面(眼底Ef) 为止的距离。 [0287] Next, the operation unit 231 magnification operation from the rear surface of the crystalline lens of the examinee's eye E distance retina face (fundus Ef of) to. 例如可以通过基于角膜曲率(曲率半径)的测定值和运算值的傍轴光线跟踪(paraxialraytrcaing)来进行该运算。 This calculation may be performed, for example, by paraxial ray tracing (paraxialraytrcaing) was measured and computed values ​​based on the corneal curvature (curvature radius). 此时,眼球的光学常数例如可以使用基于临床数据或模型眼等的标准值。 In this case, the optical constants of the eye, for example, can use a standard value based on clinical data, or the like of the model eye.

[0288] 接着,倍率运算部231运算受检眼E的眼轴长度。 [0288] Next, the axial length ratio calculation unit 231 calculating the examinee's eye E. 可以根据傍轴光线跟踪的运算结果、从角膜前表面到水晶体后表面为止的距离来进行该运算。 The calculation result can be a paraxial ray trace from the anterior corneal surface to the crystalline surface of the distance to the calculation. 该距离例如可以使用基于临床数据或模型眼等的标准值。 The distance may be used, for example, a standard value based on clinical data, or the like of the model eye.

[0289] 接着,倍率运算部231运算眼轴长度的运算结果和眼轴长度的测定结果(光学信息V)的误差,判断该误差是否包含在预定的许可范围内。 [0289] Next, calculation results and the measurement results of the ocular axial length ratio calculation unit 231 calculating the axial length (optical information V), the error determining whether the error is contained within a predetermined allowable range. 例如,求出运算结果相对于测定值的误差来作为该误差,即,求出用测定值和运算结果的差除以测定值后所得的商的绝对值来作为该误差。 For example, the calculation result is obtained with respect to the measurement error as the error value, i.e., the absolute value obtained by dividing the commercially obtained after the difference between the measured value and the measured value as the calculation result of the error. 而且,该误差的许可范围事先设为如下的临界值,该临界值是用来决定使用哪种值作为受检眼E的眼球光学系统的光学常数。 Further, the permissible range of error is set in advance below the threshold, the threshold is used to decide which value is used as the optical constants of the optical system of the eye E of the examinee's eye.

[0290] 当眼轴长度的误差包含在许可范围内时,例如,采用角膜曲率(曲率半径)的测定值以及运算结果、屈光度测定值以及眼轴长度的运算结果,来作为受检眼E的光学常数。 [0290] When the axial length of the error contained within the permissible range, e.g., using the corneal curvature (radius of curvature) of the measured values ​​and the calculation result, the calculation result diopter measurement values ​​and axial length of the examinee's eye E as the optical constants. 另外,采用眼轴长度的运算结果的二分之一值,来作为视网膜面(眼底Ef)的曲率半径。 Further, using the calculation result of the ocular axial length of one-half the value as the radius of curvature of the retina face (fundus Ef of) a. 另外,采用眼轴长度的运算结果减去从角膜前表面到水晶体后表面为止的距离的标准值(临床数据或模型眼的值)所得的值,来作为水晶体后表面到视网膜(眼底Ef)为止的距离。 Further, using the axial length of the calculation result is subtracted from the anterior corneal surface to a value obtained by (the value of clinical data or a model eye) the standard value of the distance up to the rear surface of the crystal body as a surface to the retina (fundus Ef of) the crystalline far the distance.

[0291] 另一方面,眼轴长度的误差不包含在许可范围内时,例如使用顶点屈光力以及眼轴长度的测定值来进行傍轴逆光线跟踪,由此来运算受检眼E的水晶体屈光力。 When [0291] On the other hand, the error in axial length is not included within the allowable range, for example, the vertex refractive power and axial length measurement values ​​is performed paraxial backward ray tracing, thereby calculating the crystalline form E of the examinee's eye refractive power . 而且,例如采用角膜曲率(曲率半径)的测定值以及运算结果、屈光度测定值以及眼轴长度测定值,来作为受检眼E的光学常数。 Furthermore, using e.g. corneal curvature (radius of curvature) of the measured values ​​and calculation results, and the diopter value of the ocular axial length measurement value is measured, as the optical constants of the examinee's eye E. 另外,采用眼轴长度测定值的二分之一值,来作为视网膜面(眼底Ef)的曲率半径。 Further, in one half of the axial length value measured value, as the radius of curvature of the retina face (fundus Ef of) a. 另外,采用眼轴长度测定值减去角膜前表面到水晶体后表面为止的距离的标准值(临床数据或模型眼的值)所得的值,来作为从水晶体后表面到视网膜(眼底Ef)为止的距离。 Further, the use of ocular axial length measurement value value obtained by subtracting (a value of clinical data or a model eye) the standard value of the distance up the surfaces to a crystal precursor cornea, as from the crystal surface until the retina (fundus Ef of) the distance.

[0292] 决定了受检眼E的光学常数后,倍率运算部231运算视网膜面(眼底Ef)中像的高度。 After [0292] The optical constants determined examinee's eye E, the calculation unit 231 calculating a magnification of the retina face (fundus Ef of) the image height. 该运算例如可以通过光线跟踪来进行,该光线跟踪使用有经决定的光学常数、以及对该物镜113的入射角的运算结果。 This operation can be performed by, for example, ray tracing, ray tracing using the optical constant has been decided, and the calculation result of the angle of incidence of the objective lens 113.

[0293] 最后,倍率运算部231根据视网膜面中像的高度的运算结果、检测面中像的高度的运算结果、中继(relay)透镜126的中继倍率(拍摄光学系统120等的影响)等,来运算倍率。 [0293] Finally, according to the height 231 of the calculation result in the image plane of the retina, the calculation result of the height of the image detecting surface, (Effect of the photographing optical system 120, etc.) Magnification operation of the relay (Relay) magnification of the relay lenses 126 and the like, the magnification is calculated. 该倍率是考虑到受检眼E的眼球光学系统的倍率和拍摄光学系120的倍率后而获得的倍率。 The magnification is given to the optical system magnification of the eye of the examinee's eye E and the photographing magnification of the magnification of the optical system 120 is obtained.

[0294] 另外,以上是受检眼E内并未安装眼内透镜的情况下倍率运算处理的说明。 [0294] Further, the above description is the case where the magnification of the intraocular lens is not mounted within the arithmetic processing examinee's eye E. 当受检眼E内安装着眼内透镜时,倍率运算部231使用该眼内透镜的度数等信息以进行和上述相同的运算来求出倍率。 When the examinee's eye E focus lens mounted within, magnification operation part 231 provided with intraocular lens information such as the degree and the same calculation for the above ratio is obtained. 另外,有无眼内透镜则是根据眼内透镜信息来判断的。 Further, the presence or absence of the intraocular lens is an intraocular lens according to the determination information.

[0295] 另外,当使用了校正透镜时,倍率运算部231运算该校正透镜的倍率,并考虑到该运算结果而进行和上述同样的运算,由此求出目标的倍率。 [0295] Further, when the correction lens, the magnification ratio calculation unit calculating the correction lens 231, and taking into account the calculation result and the same operation is performed above, thereby obtaining the target magnification. 另外,校正透镜的倍率可以根据校正透镜的焦距、或物镜113侧的焦点和校正透镜的物体侧主点的距离等来加以运算。 Further, the magnification of the correction lens can be focus from the distance calculation correction lens and the object side principal point of the focal length of the correction lens, the objective lens 113 side or the like.

[0296](积分图像生成部) [0296] (integral image generation unit)

[0297] 积分图像生成部233进行如下的处理:产生将断层图像Gi在深度方向(ζ方向) 上进行积分所获得的图像(积分图像)。 [0297] integral image generating unit 233 performs the following processing: the tomographic image Gi generates an image (integrated image) obtained by integrating in the depth direction (direction [zeta]). 积分图像产生部233将构成断层图像Gi的各深度方向的图像Gij在深度方向上进行积分,借此形成各扫描线Ri的位置上的点状图像。 The image Gij integral image generation unit 233 constituting the tomographic image Gi in the depth direction by integrating in the depth direction, thereby forming an image point at the position of each scanning line Ri. 积分图像由排列这些点状图像而形成。 Integral image is formed by dot-shaped images are arranged.

[0298] 在此,所谓的“在深度方向上进行积分”,是指在深度方向上对深度方向的图像Gij 的各深度位置的亮度值(像素值)进行累加的运算处理。 [0298] Here, a so-called "integrating in the depth direction" means the luminance value (pixel value) calculation processing performed at each depth position accumulated in the depth direction of the image Gij in the depth direction. 因此,对深度方向的图像Gij进行积分而获得的点状图像,具有在深度方向上将该深度方向的图像Gij的各ζ位置的亮度值进行累积而获得的亮度值。 Therefore, dot images Gij in the depth direction of the image obtained by integrating, with a luminance value of the luminance values ​​of the ζ position of the image Gij in the depth direction are accumulated in the depth direction is obtained.

[0299] 积分图像产生部233针对m个断层图像Gl〜Gm的每一个,将形成该断层图像Gi 的各深度方向上的图像Gij在深度方向上进行积分,借此在取得m个断层图像Gl〜Gm时的信号光LS的扫描区域R中,形成由二维分布的mXn个点状图像所构成的积分图像。 An image Gij in the depth direction of each of the [0299] integrated image generation unit 233 for each of m number of tomographic images Gl~Gm, the tomographic image Gi formed by integrating in the depth direction, thereby obtaining the tomographic image Gl m scanning region R of the signal light LS when ~Gm formed integral image by the two-dimensional distribution of point-like image mXn constituted.

[0300] 积分图像和扫描区域R中的眼底图像Ef相同,是表示眼底Ef的表面形态的二维图像。 [0300] the same image and the fundus image Ef integral scanning region R, is a two-dimensional image of the surface morphology of the fundus oculi Ef. 一般来说,能够用眼底相机进行拍摄的区域大于能够用OCT装置进行拍摄的区域。 In general, imaging can be larger than the area of ​​the region can be taken with a fundus camera OCT device. 眼底观察装置1是在眼底图像Ef的拍摄区域内设定扫描区域R而使用的。 Fundus oculi observation device 1 is a scanning region R set in the photographing region of the fundus image Ef used. 因此,作为积分图像而获得的区域,相当于眼底图像Ef的拍摄区域的一部分。 Thus, as the integration region image obtained, corresponding to a part of the photographing region of the fundus image Ef. 另外,眼底图像Ef的拍摄区域和扫描区域R只要各自的至少一部分重复即已足够。 Further, the fundus image Ef and the photographing region of the scanning region R is repeated as long as at least a portion of each is sufficient.

[0301](定位部) [0301] (positioning portion)

[0302] 定位部234进行眼底图像Ef和积分图像的定位。 [0302] positioned image localization section 234 and the integral image of the fundus Ef. 如上所述,积分图像相当于眼底图像Ef的一部分区域。 As described above, the integral image corresponding to a partial area of ​​the fundus image Ef. 定位部234通过确定眼底图像Ef内的积分图像的位置来进行两者的定位。 The positioning unit 234 performs positioning by determining the position of both the integral image in the fundus image Ef. 另外,当眼底图像Ef的一部分和扫描区域R的一部分重复时,定位部234进行该重复区域的定位。 Further, when a portion of a fundus image Ef and a portion of the scanning region R of the repetition, the positioning portion 234 for positioning the overlap area.

[0303] 具体说明定位部234所执行的处理。 [0303] The processing executed by the positioning unit 234 is specifically described. 首先,定位部234根据由倍率运算部231所运算出的倍率,使眼底图像Ef和积分图像的倍率一致。 First, the positioning unit 234 according to the same magnification of 231 magnification calculation section calculated, and the fundus image Ef integral image magnification. 此时,通过变更眼底图像Ef以及积分图像中至少其中之一的倍率来使两者的倍率一致。 At this time, a magnification by changing the ratio of both coincide wherein at least one of a fundus image Ef and image integration. 通过像这样预先使倍率保持一致,可以缩短定位所花费的处理时间。 By this way the magnification consistent advance, the processing time can be shortened positioning takes.

[0304] 其次,定位部234对积分图像进行分析并提取特征点。 [0304] Next, the positioning section 234 and the integral image is analyzed to extract a feature point. 例如提取血管的分支点等作为特征点。 Such as extracting a blood vessel branch point as a feature point, and the like.

[0305] 接着,定位部234对眼底图像Ef进行分析,寻找所述特征点。 [0305] Next, the positioning portion 234 for analyzing the fundus image Ef, to find the feature points. 此时,例如将眼底图像Ef (假设为彩色图像)转换为黑白(monochrome)图像,再寻找该黑白图像中的所述特征点。 In this case, for example, a fundus Ef of the image (assuming the color image) is converted to black and white (Monochrome) image, then find the feature points in the monochrome image. 该处理是针对从积分图像中提取的各特征点而进行的。 The process is directed to each feature point extracted from the image integration carried out. [0306] 接着,定位部234根据积分图像中的特征点和眼底图像Ef中的特征点,求出仿射(affine)转换的系数。 [0306] Next, the positioning unit 234 according to the feature points in the integral image and the fundus image Ef obtained affine (Affine) conversion coefficients. 二维仿射转换是由含有对应于放大/缩小或旋转的二次矩阵、以及对应于平行移动的常数矢量的式子来表示的。 Comprising a two-dimensional affine transformation is a corresponding enlargement / reduction or rotation of the quadratic matrix and constant vector corresponding to a parallel movement of the formulas to indicated. 定位部234针对积分图像中提取的各特征点,通过代入积分图像中的坐标值、及眼底图像Ef中的坐标值,而决定所述二次矩阵和常数矢量。 The positioning portion 234 integral image for each feature point extracted, by substituting the coordinate value of the integral image, and the coordinate values ​​of the fundus image Ef, determines the secondary matrix and the constant vector. 此时,也可以进行最小二乘法等近似运算。 In this case, can be approximated calculation method of least squares. 由此,决定仿射转换的系数。 Accordingly, the affine transformation coefficients determined.

[0307] 定位部234使用经决定的系数来对积分图像进行仿射转换,由此使积分图像的位置和眼底图像Ef的位置一致。 [0307] positioning unit 234 using the coefficient determined by affine transformation is performed on the integral image, whereby the position of the fundus image Ef and the image points coincide. 另外,虽然也可以转换眼底图像Ef侧,但如上所述积分图像通常相当于眼底图像Ef的一部分,所以理想的是对积分图像实施仿射转换。 Further, although it can convert the fundus image Ef side, but the integral image as described above normally corresponds to a part of the fundus image Ef, it is desirable that the integral image according to an affine transform.

[0308] 另外,在以上处理中,使积分图像和眼底图像Ef的倍率一致之后进行定位,但也可以先使断层图像的倍率一致再形成积分图像,然后进行定位。 [0308] Further, in the above process, the integration of the image and the fundus image Ef positioned after the same magnification, it is also possible to make the same magnification and then forming a tomographic image of an integral image, and then positioning.

[0309](计测位置设定部) [0309] (measurement position setting part)

[0310] 计测位置设定部235根据定位部234的积分图像和眼底图像Ef的定位结果,设定眼底Ef的计测位置。 [0310] measuring position setting unit 235 according to the positioning result of the positioning portion 234 of the integral image and a fundus image Ef is set measuring position of the fundus oculi Ef. 另外,在本实施形态中,如图17所示,将圆形计测线M1、M2、M3设定为计测位置,但可以根据计测内容来设定任意的计测位置。 Further, in the present embodiment, shown in Figure 17, circular measurement lines M1, M2, M3 is set to measuring position, but may be set to any position measurement based on the measurement content.

[0311] 说明计测位置设定部235所执行的处理的一个例子。 [0311] illustrates an example of measurement position setting processing executed by the unit 235. 首先,计测位置设定部235 对眼底图像Ef进行分析,以确定眼底图像Ef中相当于眼底Ef视神经乳头中心的位置(乳头中心位置)。 First, the measurement position setting section 235 to analyze a fundus image Ef, the fundus image Ef to determine the position of the fundus oculi Ef equivalent to the center of the optic disc (papilla center position). 该处理例如是通过如下方式来进行:对眼底图像Ef的像素值进行分析,提取亮度较高的区域(相当于视神经乳头的图像区域),求出该图像区域的重心位置并设定为乳头中心位置。 This processing is performed by: the pixel values ​​of the fundus image Ef is analyzed to extract a high luminance region (an image region corresponding to the optic papilla), obtains the gravity center position of the image region and set as the center of nipple position. 另外,也可以求出近似相当于视神经乳头的图像区域的椭圆,再求出该椭圆的中心(两个焦点间的中点)后设定为乳头中心位置。 Further, may be obtained corresponds approximately elliptical optic nerve head image area, and then obtains the center position is set as the nipple center of the ellipse (the midpoint between the two focus). 乳头中心位置的确定方法是任意的。 The method of determining the center position of the nipple is arbitrary.

[0312] 接着,计测位置设定部235在眼底图像Ef上设定计测线M1、M2、M3。 [0312] Next, the measurement position setting unit 235 to set the measurement lines M1, M2, M3 on the fundus image Ef. 为此,计测位置设定部235将经过确定的乳头中心位置设为中心C(参照图17),将半径ml = 1. 2mm的圆形区域设定为计测线Ml,将半径m2 = 1.6mm的圆形区域设定为计测线M2,将半径m3 = 2. Omm的圆形区域设定为计测线M3。 For this purpose, the measurement position setting part 235 determines the nipple through the center to center position C (see FIG. 17), the radius ml = 1. 2mm circular region is set to the measurement line of Ml, m2 = radius 1.6mm circular region is set to the measurement line M2, m3 = the radius of the circular region is set to 2. Omm measurement line M3.

[0313] 另外,计测位置设定部235确定和设在眼底图像Ef上的各计测线M1、M2、M3相对应的断层图像Gi的位置。 [0313] Further, the measurement position setting part determines and 235 disposed on the fundus image Ef the respective measurement lines M1, M2, M3 corresponding to the position of the tomographic image Gi. 对该处理进行更具体说明。 This process will be described more specifically.

[0314] 眼底图像Ef和积分图像是通过定位部234相互进行定位的。 [0314] fundus image Ef and an integral image is positioned by the positioning portion 234 to each other. 因此,眼底图像Ef 的坐标系和积分图像的坐标系可以相对应地进行坐标转换。 Thus, the fundus image Ef coordinate system and the coordinate system of the image may be integral corresponding to coordinate transformation.

[0315] 另外,相对于眼底图像Ef而定位的积分图像,是在深度方向上对断层图像Gi进行积分,进而实施所述仿射转换而获得的图像。 [0315] Further, with respect to the fundus image Ef positioned image points, is the integral of the tomographic image Gi in the depth direction, and further embodiments of the image affine transformation obtained. 因此,定义积分图像的坐标系和定义断层图像Gi的坐标系可以相对应地进行坐标转换。 Thus, the integral image defined coordinate system and define the tomographic image Gi corresponding to the coordinate system can be coordinate conversion.

[0316] 由此,定义眼底图像Ef的坐标系和定义断层图像Gi的坐标系可以进行坐标转换。 [0316] Accordingly, the definition of the coordinate system of the fundus image Ef and a tomographic image Gi of the defined coordinate system may be a coordinate conversion.

[0317] 各计测线Ml、M2、M3设定在眼底图像Ef上。 [0317] Each measurement line Ml, M2, M3 is set on the fundus image Ef. 因此,各计测线Ml、M2、M3的位置是用定义眼底图像Ef的坐标系来表示的。 Thus, the position of each measurement line Ml, M2, M3 is defined by the coordinate system of the fundus image Ef expressed. 计测位置设定部235将表示各计测线M1、M2、M3的位置的坐标值,转换为定义断层图像Gi的坐标系的坐标值。 Measuring position setting unit 235 indicating the position of each coordinate value of the measurement lines M1, M2, M3, and define the tomographic image Gi is converted to coordinate values ​​of the coordinate system. 借此,确定和各计测线M1、M2、 M3相对应的断层图像Gi上的位置。 Accordingly, the determination and the respective measurement lines M1, M2, M3 corresponding to the position on the tomographic image Gi. 计测位置设定部235将这些确定位置设定为计测位置。 Measuring position setting unit 235 is set to determine the position of these measuring position.

[0318](层厚计测部) [0318] (layer thickness measuring unit)

[0319] 层厚计测部236对由计测位置设定部235所设定的计测位置上的眼底Ef的层厚进行计测。 [0319] layer thickness measuring unit 236 performs measurement on the fundus oculi Ef by the layer thickness measuring position setting unit 235 of the measuring position. 对该计测处理进行说明。 The measurement processing will be described.

[0320] 首先,层厚计测部236求出由计测位置设定部235所设定的计测位置上的眼底Ef 的预定层的位置。 [0320] First, a layer thickness measuring section 236 obtains a predetermined position on the layer of the fundus oculi Ef measuring position setting unit 235 of the measurement position. 为此,层厚计测部236例如进行如下处理。 For this purpose, for example, a layer thickness measuring unit 236 performs the following processing.

[0321] 层厚计测部236形成经过设定的计测位置上的断层图像(计测断层图像)。 [0321] a layer thickness measuring section 236 is formed through the tomographic image (tomographic image measurement) on the set measurement position. 该处理例如可以通过下述方式来进行:确定和该计测位置相对应的立体数据的位置,并形成将该确定位置作为截面的断层图像。 This treatment can be performed in the following manner: determining the position and the measuring position corresponding to the three-dimensional data, and to determine the position of the formed tomographic image of a section. 在此,立体数据是根据断层图像Gi形成的,因此可以确定和计测位置相对应的立体数据的位置。 Here, the data is formed in accordance with stereoscopic tomographic image Gi of, and may be determined so that the position measuring position corresponding to the volume data. 另外,除了根据立体数据来形成计测断层图像以外,也可以根据断层图像Gi来形成计测断层图像。 Further, in addition to forming a measurement tomographic image data perspective, may be formed according to the measurement tomographic image is a tomographic image Gi.

[0322] 接着,为了容易地求出计测断层图像中眼底Ef的层位置,层厚计测部236实行预定的预处理。 [0322] Next, in order to easily determine the position of the measurement layer of the fundus oculi Ef in the tomographic image, the layer thickness measuring section 236 to implement predetermined preprocessing. 该预处理例如可以适当地执行灰度转换处理、图像强调处理、临界值处理、对比度转换处理、二值化处理、边缘检测处理、图像平均化处理、图像平滑化处理、滤镜处理等任意的图像处理。 The pre-treatment can be suitably performed, for example, gradation conversion processing, image enhancement processing, threshold processing, contrast conversion processing, binarization processing, edge detection processing arbitrary, image averaging, image smoothing processing, filter processing, etc. Image Processing. 另外,也可以适当地组合以执行这些图像处理。 Further, it may be appropriately combined to perform the image processing.

[0323] 接着,层厚计测部236沿着眼底Ef的深度方向,对构成实施过预处理的计测断层图像的像素的像素值(例如亮度值)逐列进行分析。 [0323] Next, a layer thickness measuring section 236 along the depth direction of the fundus oculi Ef, column by column constituting embodiment of the pixel values ​​(e.g., luminance value) of pixels of the tomographic image measuring pretreated analyzed.

[0324] 也就是说,计测断层图像是由沿着和计测位置相对应的截面排列的多个深度方向的图像Gij(以及插入这些图像间的深度方向的图像)所构成。 [0324] That is, the measurement tomographic image is composed of a plurality of measuring position and along a depth direction of cross section corresponding to the arrangement of an image Gij (insertion depth direction and an image between the images of these). 层厚计测部236分别针对这些深度方向的图像,通过沿着深度方向依次参照构成此深度方向的图像的像素的像素值, 来确定相当于邻接的层边界位置的像素。 The pixel values ​​of the layer thickness measuring unit 236 for images of the depth direction, the reference image by sequentially constituting the depth direction along the depth direction of pixels is determined corresponding to a pixel adjacent to the boundary position of the layer. 此时,使用仅在深度方向上具有空间的滤镜(例如微分滤镜),来确定相当于层的边界位置的像素。 In this case, only the filter having a space (e.g., differential filter) in the depth direction, and determines the pixel position corresponding to the boundary layer.

[0325] 另外,先前在确定层位置的处理中,使用在深度方向以及与之垂直的方向此两个方向上扩大的滤镜(区域滤镜),来进行断层图像的边缘检测。 [0325] Further, in the process previously determined location layer, in a depth direction and the direction perpendicular thereto expansion of these two directions filters (filter region), to detect the edge of the tomographic image. 另一方面,在本实施形态中, 使用仅在深度方向上具有空间的一维滤镜(线性滤镜)来进行深度方向上的边缘检测,由此缩短了边缘检测所花费的处理时间。 On the other hand, in the present embodiment, the use of only one dimensional spatial filter (linear filter) to detect an edge in the depth direction, thereby shortening the processing time takes the edge detection in the depth direction. 而且,通过进行这样的处理,能够以良好的精度来进行边缘检测。 Further, by performing such processing can be performed with good accuracy edge detection. 该边缘检测用的线性滤镜可以预先存储在硬盘驱动器204等中。 The linear edge detecting filter may be stored in the hard disk drive 204 or the like in advance. 另外,也可以使用和先前相同的边缘检测处理。 Further, the same can also be used and the previous edge detection processing.

[0326] 而且,层厚计测部236能够求出该计测断层图像中相当于眼底Ef的层的边界位置的图像区域,同时能够求出相当于眼底Ef的层的图像区域。 [0326] Further, the layer thickness measuring section 236 can obtain an amount corresponding to the image region of the boundary layer of the fundus oculi Ef position measurement tomographic image, at the same time it can be determined corresponding to the image regions of the layer of the fundus oculi Ef. 也就是说,眼底Ef是由多个层所构成,因此,确定层和确定层的边界位置,意义是相同的。 That is, the fundus oculi Ef is composed of a plurality of layers, therefore, is determined and the layer boundary positions to determine layer, are synonymous.

[0327] 眼底Ef从眼底表面侧朝向深度方向依次具有视网膜、脉络膜、巩膜。 [0327] fundus oculi Ef depth direction from the surface side having the fundus order retina, choroid, sclera. 而且,视网膜从眼底表面侧朝向深度方向依次具有内界膜、神经纤维层、神经节细胞层、内网状层、内颗粒层、外网状层、外颗粒层、外界膜、视细胞层、视网膜色素上皮层(有时也因眼底Ef的部位不同而不同)。 Furthermore, retinal depth direction from the surface of the fundus order side having an inner limiting membrane, nerve fiber layer, ganglion cell layer, inner plexiform layer, the granular layer, outer plexiform layer, outer nuclear layer, external limiting membrane, photoreceptor cell layer, retinal pigment epithelial (sometimes due to the site of the fundus oculi Ef differ). 层厚计测部236求出这些层中至少任一层的层位置(层的边界位置)。 A layer thickness measuring section 236 obtains the layer position of at least any one of these layers (boundary layer positions).

[0328] 在此,“层”包括构成视网膜的所述各层,而且也包括脉络膜、巩膜、或其外部组织等。 [0328] Here, "layer" includes layers constituting the retina, but also the choroid, sclera, or external organization. 另外,层的边界位置包括构成视网膜的所述层的边界位置,而且也包括内界膜和玻璃体的边界位置、视网膜色素上皮层和脉络膜的边界位置、脉络膜和巩膜的边界位置、巩膜和其外部组织的边界位置等。 Further, the position of the boundary layer comprises a layer composed of the boundary position of the retina, but also the position of the boundary of the internal limiting membrane and the vitreous, the boundary position of the retinal pigment epithelium and choroid, choroid and sclera boundary position, and its outer sclera border location and other organizations.

[0329] 层厚计测部236进行如下处理:根据计测断层图像中眼底Ef的预定层的位置,来运算眼底Ef的预定部位的厚度。 [0329] layer thickness measuring unit 236 performs the following processing: According to the position of the tomographic image measuring a predetermined layer of the fundus oculi Ef, calculates the thickness of a predetermined portion of the fundus oculi Ef. 在此,所谓的眼底Ef的预定部位,是指所述眼底Ef的多个层中一个以上的层的部位。 Here, the predetermined portion of the fundus oculi Ef, means a site of the fundus oculi Ef in a plurality of layers in more than one layer. 例如,视网膜色素上皮层单独相当于“预定部位”,内界膜到内颗粒层为止的多个层也相当于“预定部位”。 For example, the retinal pigment epithelium alone corresponds to the "predetermined site", a plurality of internal limiting membrane to the inner layers until the particle layer also corresponds to the "predetermined site."

[0330] 而且,成为厚度运算对象的“预定部位”,有例如内界膜到神经纤维层为止的厚度(神经纤维层厚)、内界膜到内颗粒层(视细胞的内切.外切)为止的厚度(视网膜厚;第1定义)、内界膜到视网膜色素上皮层为止的厚度(视网膜厚;第2定义)等。 [0330] Further, a "predetermined site" operation target thickness, for example, to a thickness (nerve fiber layer thickness) until the nerve fiber layer, the granular layer to the inner limiting membrane (endo visual cells ILM. Exo ) thickness (up to a thickness of the retina; a first definition), the thickness of the internal limiting membrane (retina thickness retinal pigment until the cortex; second definition) and the like.

[0331] 如上所述,层厚计测部236能够求出计测断层图像中眼底Ef的层的位置(边界位置)。 [0331] As described above, the layer thickness measuring unit 236 can determine the position (boundary position) layer measurement tomographic image of the fundus oculi Ef. 此时,求出至少两个边界位置。 At this time, to obtain at least two boundary positions. 层厚计测部236运算所求出的边界位置中预定的两个边界位置间的距离,由此求出目标层的厚度。 Boundary layer thickness measuring position calculation section 236 by a predetermined distance determined between the two boundary positions, thereby obtaining the target layer thickness.

[0332] 更具体来说,层厚计测部236针对构成计测断层图像的各深度方向的图像,来运算分别相当于该预定的两个边界位置的像素之间的距离(深度方向的距离)。 [0332] More specifically, the layer thickness measuring unit 236 for constituting the image measurement depth direction of the tomographic image, and calculates distance correspond (in the depth direction between two boundary pixels of the predetermined positions ). 此时,对深度方向的图像的各像素,分配所述xyz坐标系的坐标值(χ坐标值、y坐标值分别固定)。 In this case, the image in the depth direction for each pixel, assigning the xyz coordinate values ​​(coordinate values ​​of [chi], y-coordinate values ​​are fixed) coordinate system. 层厚计测部236可以根据这些坐标值来运算像素间的距离。 A layer thickness measuring section 236 can calculates the distance between pixels from these coordinate values. 另外,层厚计测部236也可以根据分别相当于该预定的两个边界位置的像素之间的像素数、及邻接像素间的距离(已知),来运算目标的距离。 Further, the layer thickness measuring section 236 may also correspond to a distance between pixels of the number of pixels between two predetermined boundary position, and the adjacent pixels (known), calculates the target distance.

[0333] 在本实施形态中,设定圆形计测线M1、M2、M3。 [0333] In the present embodiment, circular measurement lines set M1, M2, M3. 因此,层厚计测部236对和各计测线Ml、M2、M3相对应的计测断层图像求出层厚度。 Thus, the layer thickness measuring section 236 pairs and the respective measurement lines Ml, M2, M3 corresponding to the obtained tomographic image measuring the layer thickness. 各计测断层图像是具有圆柱状截面的断层图像。 Each measurement tomographic image is a tomographic image having a cylindrical cross-section. 层厚计测部236针对各计测断层图像,例如,以1度的间隔(也就是在圆周上的360 处)求出层的厚度。 A layer thickness measuring section 236, for each measurement tomographic image, for example, at intervals of 1 degree (i.e. on the circumference at 360) obtains thickness of the layer.

[0334] 层厚计测部236也可以根据以所述方式求出的层厚度,来形成显示经过设定的计测位置的层厚度分布的层厚图表信息。 [0334] a layer thickness measuring section 236 may be determined in the manner described according to the layer thickness, is formed through the thickness of the display layer thickness measuring position setting information distribution graph. 另外,层厚计测部236进行动作以将所求出的层厚度归纳为预定的输出形式(模板)。 Further, the layer thickness measuring section 236 is operated to the obtained layer thickness summarized predetermined output format (template).

[0335][使用形态] [0335] [Use Mode]

[0336] 说明具有如上结构的眼底观察装置1的使用形态。 [0336] having the above described structure of the fundus observation device 1 forms used. 图10所示的流程图表示眼底观察装置1的使用形态的一个例子。 The flowchart shown in FIG. 10 shows an example of an apparatus using the embodiment 1 of the fundus observation.

[0337] 首先,测定受检眼E的角膜曲率、屈光度以及眼轴长度(Si)。 [0337] First, the measurement of the cornea curvature, refractive power and axial length of the examinee's eye E (Si). 该测定例如是使用专用的检查装置来进行。 The assay is performed, for example, using a dedicated inspection device. 这些测定值经过通信线路或存储媒体而输入到眼底观察装置1中, 作为光学信息V而存储在存储部212中。 These measured values ​​via a communication line or a storage medium and input to the fundus oculi observation device 1, as the optical information V stored in the storage unit 212. 眼内透镜信息也被输入到眼底观察装置1并作为光学信息V而加以存储。 Intraocular lens information is also inputted into the fundus oculi observation device 1 as the optical information V and stored.

[0338] 使用眼底观察装置1,取得受检眼E的眼底图像Ef以及断层图像Gi (S2)。 [0338] using the fundus oculi observation device 1 acquires a fundus image Ef and a tomographic image Gi of the examinee's eye E (S2). 所取得的眼底图像Ef以及断层图像Gi存储在存储部212中。 In the storage unit 212 in the fundus image Ef and a tomographic image Gi stored acquired.

[0339] 另外,角膜曲率等的测定及受检眼E的图像取得中的任一个均可先行进行。 [0339] Further, any of the image acquisition and measurement of corneal curvature in the examinee's eye E can first be a. 而且, 角膜曲率等的测定无需像本使用形态那样以一系列流程来进行,也可以使用以往另行测定的值。 Also, measurement of the cornea curvature need not be performed as a series of image process using this form, may be used separately measured values ​​of the conventional.

[0340] 取得光学信息V、眼底图像Ef以及断层图像Gi后,倍率运算部231根据光学信息V,来运算受检眼E的眼球光学系统的倍率(S3)。 After the [0340] acquired optical information V, the fundus image Ef and a tomographic image Gi, magnification operation part 231 according to the optical information V, calculates the magnification of the optical system of the eye E of the examinee's eye (S3).

[0341] 其次,积分图像形成部233通过对断层图像Gi在深度方向上进行积分而形成积分图像(S4)。 [0341] Next, the image forming unit 233 by integrating tomographic image Gi in the depth direction is integrated to form an integral image (S4). 定位部234根据步骤3中运算出的倍率,来对眼底图像Ef和积分图像进行定位(S5)。 The positioning portion 234 calculated in Step 3 of magnification, the positioning is performed (S5) on the fundus image Ef and the integral image.

[0342] 接着,计测位置设定部235根据眼底图像Ef和积分图像的定位结果,在断层图像Gi中设定和各计测线M1、M2、M3相对应的计测位置(S6)。 [0342] Next, the measurement position setting unit 235 according to the positioning result of the fundus image Ef and the integral image, is set in the tomographic image Gi and the respective measurement lines M1, M2, M3 corresponding to the measuring position (S6). 此时,也可以对基于断层图像Gi的三维图像(立体数据)来设定计测位置,以代替在断层图像Gi中设定计测位置。 In this case, a tomographic image Gi may be for three-dimensional image (volume data) based on the measuring position is set, instead of setting the measurement position of the tomographic image Gi.

[0343] 其次,层厚计测部236形成和各计测线M1、M2、M3相对应的计测断层图像(S7)。 [0343] Next, 236 is formed, and the layer thickness of the respective measurement lines M1 measurement unit, M2, M3 corresponding to the measurement tomographic image (S7). 另外,层厚计测部236对各计测断层图像进行分析,确定预定层的位置(S8)。 Further, the layer thickness measuring part 236 analyzes each of the measurement tomographic images, determining the position of a predetermined layer (S8).

[0344] 主控制部211将步骤7中形成的计测断层图像、及步骤8中确定的层位置(边界位置)显示在显示部MOA中(S9)。 [0344] The main control unit 211 in the measurement tomographic image formed in step 7 and step 8 is determined slice position (boundary position) on the display unit to MOA (S9). 此时,可以全部显示和计测线M1、M2、M3相对应的计测断层图像,也可以选择显示这些图像中的任一个。 In this case, all the display and the measurement lines M1, M2, M3 corresponding to the measurement tomographic image, the display may select any of these images.

[0345] 图11表示计测断层图像以及层位置的显示形态的一个例子。 [0345] FIG. 11 shows a measurement example of a tomographic image and a layer position of the display mode. 在图11所示的显示形态中,显示计测断层图像G,并且显示层位置图像Li、L2、L3、L4,这些层位置图像Li、L2、 L3、L4表示对所述计测断层图像G进行分析后确定的层位置(边界位置)。 In the display mode illustrated in FIG. 11, the display measurement tomographic image G, and the position of the image display layer Li, L2, L3, L4, the position of the image layers Li, L2, L3, L4 represents a measurement tomographic image G of the count after analyzing the determined layer position (border position).

[0346] 当显示该计测断层图像时,眼底血管所存在的区域中,有时会由于因血管壁或血液引起信号光LS散射的影响等而使图像变得不清晰。 [0346] When displaying a tomographic image of the measurement region of the fundus blood vessel is present, it is sometimes due to blood vessel wall or blood caused by the influence of the scattering of the signal light LS and the like the image becomes unclear. 图11所示的图像区域H表示这样的不清晰的图像区域。 Image region H shown in FIG. 11 represent such an unclear image region. 对不清晰的图像区域H中的层位置进行高精度检测是较为困难的。 Layer position of unclear image region H is detected with high accuracy it is more difficult. 此时,如以下的说明,可以一边观察计测断层图像G—边以手动来编辑层位置。 At this time, as described below, can be measured while observing the tomographic image side to manually edit the G- layer position.

[0347] 检测者首先对操作部MOB进行操作,指定编辑对象区域,也就是指定不清晰的图像区域H(SlO)。 [0347] First, the examiner operates the operation unit MOB, designated edit target area is designated unclear image region H (SlO). 该指定操作例如是通过拖曳鼠标206来进行的。 This designation operation is performed, for example, by dragging the mouse 206. 另外,也可以删除经指定的图像区域H内的图像。 Further, the image may be deleted within the image area specified by H.

[0348] 图12表示经指定的图像区域H以及其周边的放大图像。 [0348] FIG. 12 shows a designated image region H and the periphery of the enlarged image. 检测者观察计测断层图像G,把握图像区域H中的层位置。 Detector observes the measurement tomographic image G, to grasp the position of the image layer in the region H. 然后,检测者对操作部MOB进行操作,将所把握的层位置输入到图像区域H上(Sll)。 Then, the examiner operates the operation unit MOB, the grasped layer position on the image area is input to the H (Sll). 该操作例如是通过鼠标206的单击(click)操作来进行的。 This operation is carried out, for example, by clicking mouse 206 (the Click) operation. 另外,图12的符号P表示鼠标指针。 Further, reference numeral 12 denotes a mouse pointer P.

[0349] 图13表示层位置的输入方法的一个例子。 [0349] Example 13 represents a position of the input layer of the method of FIG. 检测者操作鼠标206,使鼠标指针P移动到所把握的层位置并进行单击。 Operates the mouse 206 detected by the mouse pointer P is moved to a position to grasp the layer and click. 主控制部211使点图像Q显示在通过单击操作所指定的位置上。 The main control unit 211 through the display dot image Q clicking operation on the designated location. 图13的点图像Q表示和层位置图像Ll对应的图像区域H内的层位置。 FIG dot image Q 13 represents the position of the inner layer and the Ll layer corresponding to the position of the image area of ​​the image H.

[0350] 层厚计测部236根据检测者所输入的层位置,求出图像区域H中的层位置(S12)。 [0350] The thickness of the layer measuring portion 236 inputted by the position detection obtained in the image region H layer position (S12). 举例来说,在指定了点图像Q时,层厚计测部236求出通过各点图像Q的线(样条(spline) 曲线等)。 For example, when the designated image point Q, the layer thickness measuring section 236 obtains an image through the point Q of the line (spline (spline) curve). 另外,也可以求出根据各点图像Q的位置所获得的任意的近似曲线(例如贝赛尔(Bezier)曲线)。 It is also possible to obtain an arbitrary curve approximation (e.g. Bessel (a Bezier) curve) according to the position of each point image Q is obtained. 另外,理想的是不仅通过参照点图像Q,而且通过参照图像区域H附近的层位置图像Ll等的状态(倾斜等),而求出图像区域H内的层位置,以使其和层位置图像Ll平滑地连接。 Further, it is desirable not only by referring to the image point Q, and H through the vicinity of the position of the reference image an image area of ​​the layer Ll and the like (tilt), and the obtained layer position within the image region H, so that it and the layer position image Ll are smoothly connected.

[0351] 主控制部211将表示所求出的层位置的图像(编辑图像)显示在图像区域H内 [0351] The main control unit 211 indicating the obtained image (edited image) is displayed in a layer position within the image region H

(513)。 (513). 图14表示基于图13的点图像Q的编辑图像Ll'的显示形态。 14 shows Ll 'display mode based on the point image Q in FIG. 13 edited image.

[0352] 步骤10〜步骤13的处理在本申请人提出的日本专利特愿2006-252953中有详细记载。 Processing [0352] Step 10~ 2006-252953 step 13 described in detail in Japanese Patent No. proposed by the present applicant. 另外,也可以不进行如上所述的层位置的编辑。 Further, the layer may not edit position as described above. 此时,理想的是不计测不清晰的图像区域H内的层厚度。 In this case, it is desirable that the layer thickness is not measured in the unclear image region H. 其原因在于防止获得不正确的计测结果。 The reason for this is to prevent obtaining incorrect measurement results.

[0353] 确定层的位置后,层厚计测部236根据经确定的层位置来计测预定层的厚度 [0353] After determining the position of the layer, the layer thickness measuring section 236 in accordance with the determined position of the layer to a predetermined layer thickness is measured

(514)。 (514).

[0354] 另外,层厚计测部236将层厚度的计测结果归纳为预定的输出形式。 [0354] Further, the layer thickness measuring section 236 of the layer thickness measurement result summarized as a predetermined output format. 该输出形式例如是分别针对三个计测断层图像,将朝上、朝下、鼻方向以及耳方向之各方向的计测结果归纳为表格形式。 The output for each example in the form of three measurement tomographic images, the up, down, results of the measurement direction and the direction of the nose of the tab direction summarized in tabular form. 另外,该计测结果中,也可以记录光学信息V等和受检眼E相关的信息、或和被检测者相关的信息(患者ID或患者姓名等)。 Further, the measurement result, the optical information V may be recorded and other information related to the examinee's eye E, or information (a patient ID or patient name, etc.) and associated test subject. 计测结果是用打印机(图中未示)来印刷,或者通过通信线路送到服务器等。 Measurement results are obtained with a printer (not shown) is printed, or the like to the server via a communication line.

[0355][作用、效果] [0355] [Operation and Effect]

[0356] 说明如上所述的眼底观察装置1的作用以及效果。 [0356] As already discussed above fundus observation device 1 and effects.

[0357] 眼底观察装置1是一种OCT装置,其检测基于低相干光LO的干涉光LC,并根据其检测结果来形成眼底Ef的断层图像Gi。 [0357] fundus oculi observation device 1 is an OCT device that detects based on low-coherence light LO of the LC interference light, and forming a tomographic image Gi of the fundus oculi Ef based on the detection result. 所形成的断层图像Gi是和表示受检眼E的眼球光学系统状态的光学信息V —起存储在存储部212中。 Tomographic image Gi formed is examinee's eye E and the eye showing the optical system of the state of the optical information V - from 212 stored in the storage unit. 倍率运算部231根据光学信息V来运算受检眼E的眼球光学系统的倍率。 Ratio calculating unit 231 calculates optical information V magnification of the optical system of the eye E of the examinee's eye. 分析部232根据该倍率来分析断层图像Gi。 Analysis section 232 analyzes the tomographic image Gi based on the magnification. 特别是在本实施形态中,能够通过分析断层图像Gi,来求出眼底Ef的层的厚度。 Especially in the present embodiment, it is possible by analyzing the tomographic image Gi of, obtains the thickness of the layer of the fundus oculi Ef.

[0358] 根据像这样发挥作用的眼底观察装置1,可以根据表示受检眼E的眼球光学系统的状态的光学信息V来运算倍率。 [0358] The functioning like this fundus oculi observation device 1, the magnification can be operational state of the optical information V indicates the optical system eye E of the examinee's eye. 特别是不必像先前那样使用古尔斯特兰德模型眼的屈光力来进行推算处理。 In particular, do not like to use refractive power as previously Gullstrand eye model to calculate process. 所以,根据眼底观察装置1,可以高精度地求出受检眼E相应的倍率。 Therefore, according to the fundus observation device 1, can be determined with high accuracy corresponding to the examinee's eye E ratio.

[0359] 而且,眼底观察装置1在受检眼E内安装着眼内透镜时,根据该眼内透镜的度数等信息来发挥倍率运算的作用。 When [0359] Further, the fundus oculi observation device 1 focusing lens mounted within the examinee's eye E, the intraocular lens according to the degree of magnification information to function operation. 所以,对于安装了眼内透镜的受检眼E,也可以高精度地求出倍率。 Therefore, the intraocular lens mounting examinee's eye E, the magnification can be obtained with high accuracy.

[0360] 而且,眼底观察装置1具备形成断层图像Gi的功能,并且具备拍摄眼底Ef表面的二维图像(眼底图像Ef)的功能。 [0360] Further, the fundus oculi observation device 1 includes a function of forming the tomographic image Gi of the fundus oculi Ef and the photographing surface includes a two-dimensional image (fundus image Ef) function. 所拍摄的眼底图像Ef是存储在存储部212中。 The photographed fundus image Ef 212 is stored in the storage unit. 分析部232在眼底Ef的深度方向上对各断层图像Gi进行积分,以形成积分图像。 Analysis unit 232 integrating each tomographic image Gi in the depth direction of the fundus oculi Ef, to form an integral image. 另外,分析部232 根据倍率运算部231所求出的高精度倍率,进行眼底图像Ef和积分图像的定位。 Further, the analysis unit 232 according to a magnification operation unit 231 magnification obtained with high accuracy, the positioning image Ef and the fundus integral image. 所以,根据眼底观察装置1,可以高精度地进行眼底图像Ef和积分图像的定位。 Therefore, according to the fundus oculi observation device 1, the image may be positioned integral image Ef and the fundus accurately. 由此,可以高精度地进行眼底图像Ef和断层图像Gi (以及眼底Ef的三维图像)的定位,从而可以高精度地使眼底图像Ef上的位置和断层图像Gi上的位置相对应。 This enables the fundus image Ef and the tomographic images Gi (and the three-dimensional image of the fundus oculi Ef) is positioned with high accuracy, thereby accurately the position of the tomographic image Gi and the position on the fundus image Ef, respectively.

[0361] 而且,分析部232发挥如下的作用:根据眼底图像Ef和积分图像的定位结果来设定眼底Ef的计测位置,并根据断层图像Gi (或三维图像)来求出此计测位置上的眼底Ef 的层厚度。 [0361] Further, the analysis unit 232 play the following role: measuring position is set according to the positioning result of the fundus oculi Ef and the fundus image Ef integral image, and a tomographic image Gi (or three-dimensional images) to obtain this measuring position the layer thickness of the fundus oculi Ef. 根据眼底观察装置1,如上所述,可以高精度地使眼底图像Ef上的位置和断层图像Gi上的位置相对应,因此可以在断层图像Gi上高精度地设定该计测位置。 Fundus oculi observation device 1, as described above according, possible to accurately position and the position of the tomographic image Gi on the corresponding fundus image Ef, it is possible to accurately set the measuring position on the tomographic image Gi. 所以,根据眼底观察装置1,可以减少因眼底图像Ef和断层图像Gi的位置错位所引起的计测误差。 Therefore, according to the fundus observation device 1, it is possible to reduce the positional deviation measurement error due to the fundus image Ef and the tomographic image Gi caused.

[0362][变化例] [0362] [variant]

[0363] 以上详述的结构不过是用以实施本发明的眼底观察装置的一个例子。 [0363] However, the above structure is described in detail for an example embodiment of the fundus observation device according to the present invention. 因此,可以在本发明主旨的范围内适当实施任意的变化。 Thus, any embodiment may be appropriately varied within the scope of the gist of the present invention.

[0364] 在所述实施形态中,将眼底图像Ef和积分图像的定位结果用于眼底的层厚度的计测,但其利用方法并不限于此,例如,可以使用此定位结果,来提高信号光LS的扫描精度。 [0364] In the embodiment, the positioning result fundus image Ef and the integral image for measuring the layer thickness of the fundus, but the method is not limited to this use, for example, using this positioning result, to improve signal scanning accuracy of light LS. 以下说明其具体例。 Specific examples thereof described below.

[0365] 扫描区域R的设定大多是参照眼底图像Ef来进行的。 [0365] Most of the scanning region R is set with reference to the fundus image Ef is carried out. 然而,由于受检眼E的眼球光学系统的影响,可能会导致眼底图像Ef上的位置和信号光LS的扫描位置错位。 However, due to the optical system of the eye E of the examinee's eye, it may cause the scanning position of the signal light LS on the fundus image Ef misalignment. 如果产生这样的错位,则可能会取得一种位置和根据眼底图像Ef而设定的位置(截面)不同的断层图像,那样就必须进行再次检查。 If such a displacement, the position might strike a fundus image Ef and the position of the set (cross-section) different from the tomographic image, so it must be checked again. 而且,一边考虑这样的错位一边在眼底图像Ef上设定截面,这对于尚未熟习检查的检测者来说极为困难。 Furthermore, by taking into consideration such offset setting section in the side of the image Ef of the fundus, which has not been extremely difficult for those skilled in the detection is checked.

[0366] 所以,在本变化例中,通过进行如下处理,来解决这种问题。 [0366] Therefore, in this variation, by performing the following processing, to solve this problem. 首先,拍摄眼底图像Ef并设定截面,取得断层图像Gi。 First, shoot fundus image Ef and setting section to obtain a tomographic image Gi. 接着,根据断层图像Gi来形成积分图像,并和眼底图像Ef 进行定位。 Next, the tomographic image Gi formed integral image, and the fundus image Ef and positioning.

[0367] 分析部232根据该定位的结果来设定眼底Ef上的扫描位置。 [0367] Analysis unit 232 sets a scanning position on the fundus Ef based on the result of the positioning. 该处理可以通过如下方式来进行:根据定位处理中的所述坐标转换,使设定在眼底图像Ef上的扫描位置和积分图像(断层图像Gi)的位置相对应。 The process may be carried out by the following manner: The positioning of the coordinate conversion processing, the setting on the fundus image Ef and the position of the scanning integral image (tomographic image Gi) corresponding to a position.

[0368] 主控制部211控制镜片驱动机构M1J42,以使信号光LS在经过设定的扫描位置上受到扫描(参照图5)。 [0368] The main control unit 211 controls the lens driving mechanism M1J42, so that the signal light LS is scanned (refer to FIG. 5) through the scanning position set on. 由此,可以取得眼底图像Ef上的所需截面的断层图像。 Thereby, it is possible to obtain a tomographic image of the desired cross-section on the fundus image Ef.

[0369] 所述实施形态的眼底观察装置1是傅立叶频率领域(Domain)型OCT装置,但是对于时域(Time Domain)型、全场(Full Field)型、扫频源(SweptSource)型等任意类型的OCT装置,也均可以适用本发明的结构。 [0369] The embodiment of the fundus oculi observation device 1 is the Fourier frequency field (the Domain) type OCT device, but for the time domain (Time Domain) type, FT (Full Field) type, swept source (SweptSource) any other type type OCT apparatus, the structure of the present invention are also applicable.

[0370][关于眼底图像处理装置] [0370] [on the fundus image processing apparatus]

[0371] 对本发明的眼底图像处理装置加以说明。 [0371] will be described fundus image processing apparatus according to the present invention.

[0372] 眼底图像处理装置例如是包含以可通信方式连接于眼底相机或OCT装置的计算机而构成。 [0372] for example, a fundus image processing apparatus comprising a computer communicatively connected to the fundus camera or the OCT apparatus is constituted. 另外,眼底图像处理装置是包含如下计算机而构成,此计算机可以通过存储媒体来接受由眼底相机或OCT装置取得的图像。 In addition, a fundus image processing apparatus comprising the computer is configured, the computer can accept a fundus image acquired by the camera or the OCT apparatus via a storage medium. 此计算机具备微处理器、RAM、ROM、硬盘驱动器等(参照图4)。 This computer includes a microprocessor, RAM, ROM, a hard disk drive (see FIG. 4). 另外,此计算机的结构可以和图7所示的运算控制装置200相同。 Further, the structure and operation of this computer can control apparatus shown in FIG. 7 the same as 200.

[0373] 眼底图像处理装置是包含具备存储元件、运算元件以及分析元件的计算机而构成。 [0373] fundus image processing apparatus includes a storage device comprising a computer, a computing element and an analysis element is configured. 存储元件存储受检眼的眼底断层图像、以及表示受检眼的眼球光学系统状态的光学信息。 Fundus tomographic image of the examinee's eye is stored in the storage element, and the optical information indicates a state of the optical system of the eye of the examinee's eye. 运算元件根据存储元件所存储的光学信息,来运算受检眼E的眼球光学系统的倍率。 The optical element calculation information stored in the memory element, calculates the magnification of the optical system of the eye E of the examinee's eye. 分析元件根据所运算的倍率,对存储元件中存储的断层图像进行分析。 Analysis element according to the calculated magnification tomographic image stored in the storage element analysis.

[0374] 另外,在所述运算控制装置200中,存储部212是存储元件的一个例子,倍率运算部231是运算元件的一个例子,分析部232是分析元件的一个例子。 [0374] Further, in the arithmetic control device 200, the storage unit 212 is an example of a storage element, magnification operation part 231 is an example of the operation element analysis part 232 is an example of the analysis element.

[0375] 根据这样的眼底图像处理装置,可以依据表示受检眼的眼球光学系统状态的光学信息来运算倍率,从而不需要像先前那样使用古尔斯特兰德模型眼的屈光力来进行推算处理,因此可以高精度地求出和受检眼相对应的倍率。 [0375] Such a fundus image processing apparatus, optical information can be based on the state of the optical system of the eye showing the magnification of the subject's eye is calculated, so that no refractive power as that previously used Gullstrand eye model estimation processing is performed It can be accurately calculated and thus the subject eye corresponding to the magnification.

[0376] 另外,可以使用和所述实施形态的运算控制装置200同样结构的眼底图像处理装置。 [0376] Further, similar embodiments may be used and the configuration of the fundus image processing apparatus aspect of the arithmetic and control unit 200. 由此,和运算控制装置200相同,眼底图像处理装置可以对安装着眼内透镜的受检眼进行处理。 Thus, the same arithmetic and control unit 200, a fundus image processing apparatus may process the examinee's eye lens is installed within the focus. 另外,眼底图像处理装置也可以进行积分图像的形成处理、或眼底图像和积分图像的定位处理。 Further, the fundus image processing apparatus may be integral image forming process, or positioning processing integral image and the fundus image. 另外,眼底图像处理装置也可以进行计测位置的设定处理、以及眼底的层厚度的计测处理。 Further, the fundus image processing apparatus may be set position measuring process, the measurement process and the layer thickness of the fundus.

Claims (11)

1. 一种眼底观察装置,其特征在于包括:图像形成元件,利用拍摄光学系统的拍摄,以光学方式取得数据后,形成受检眼的眼底断层图像;存储元件,存储显示所述受检眼的眼球光学系统状态的光学信息; 运算元件,根据所述光学信息,运算所述眼球光学系统的倍率并运算所述拍摄光学系统的倍率;以及分析元件,包含计测位置设定元件,设定所述眼底的计测位置,且所述分析元件根据所述眼球光学系统的倍率与所述拍摄光学系统的倍率,对所述断层图像进行分析,并求出由所述计测位置设定元件所设定的所述计测位置的所述眼底的层厚度。 A fundus observation device comprising: an image forming element, by the imaging photographing optical system, after obtaining data optically to form a tomographic image of the fundus of the examinee's eye; storage elements, storing the examinee's eye displayed eyeball optical system of the optical information state; computing element, according to the magnification of the optical information calculates the eye optical system and calculates the photographing magnification of the optical system; and analysis element, comprising a measuring position setting member, the setting the fundus measuring position and the imaging magnification of the optical system of the analysis element according to the magnification of the optical system of the eye, the tomographic image is analyzed, and the setting element is determined by the measuring position the set position of the measuring layer thickness of the fundus.
2.根据权利要求1所述的眼底观察装置,其特征在于,所述光学信息包括所述受检眼的角膜曲率、屈光度以及眼轴长度中的至少一个测定值。 2. The fundus oculi observation device according to claim 1, wherein the optical information includes the examinee's eye corneal curvature, refractive power and axial length of the at least one measured value.
3.根据权利要求2所述的眼底观察装置,其特征在于,所述光学信息包括眼内透镜信息,此眼内透镜信息显示所述受检眼内是否安装着眼内透镜,所述运算元件根据所述眼内透镜信息来判断有无眼内透镜,当判断存在眼内透镜时, 则取代所述屈光度的测定值,而根据安装在所述受检眼内的眼内透镜的度数,对所述眼球光学系统的倍率进行运算。 3. The fundus oculi observation device according to claim 2, wherein the optical information includes intraocular lens information, lens information display is installed within the focus intraocular lens within the eye of the subject, according to the calculation member the intraocular lens information to determine the presence or absence of intraocular lens, when it is determined the presence of the intraocular lens, the measured value of the substituted refractive power, and the intraocular lens is mounted in the degree of the examinee's eye, on the magnification of said optical system computes the eyeball.
4.根据权利要求1所述的眼底观察装置,其特征在于, 所述图像形成元件拍摄所述眼底表面的二维图像,所述分析元件在所述眼底的深度方向上积分所述断层图像而形成积分图像,并根据所述眼球光学系统的倍率,对所述二维图像和所述积分图像进行定位,所述计测位置设定元件根据所述定位的结果,来设定所述眼底的计测位置,并根据所述断层图像,求出所述计测位置的所述眼底的层厚度。 4. The fundus oculi observation device according to claim 1, wherein said image forming element captured two-dimensional image of the fundus surface, the said analysis element integrated in the depth direction of the fundus tomographic image integral image is formed, according to the magnification of the optical system of the eye, and the image of the two-dimensional integral image positioning, the position sensing element is set according to a result of the positioning of the setting of the count fundus measuring position, and based on the tomographic image of the fundus to obtain a layer thickness of the measuring position.
5.根据权利要求4所述的眼底观察装置,其特征在于,所述分析元件确定所述二维图像中相当于视神经乳头中心的位置,并将以所述经确定的位置为中心且具有预定半径的圆形区域设为所述计测位置。 The fundus oculi observation device according to claim 4, characterized in that the position determination element corresponding to the two-dimensional image analysis of a center of the optic nerve head, and to the determined location and having a predetermined center the radius of the circular region is set to the measuring position.
6.根据权利要求4所述的眼底观察装置,其特征在于,所述分析元件根据所述定位结果来设定对所述眼底的扫描位置, 所述图像形成元件根据所述经设定的扫描位置,对所述眼底进行光学扫描而取得新数据,并根据该经取得的新数据来形成所述眼底的新断层图像。 6. The fundus oculi observation device according to claim 4, characterized in that the analysis element is set to the fundus scanning position based on the positioning result, the image forming element by scanning said set based on position, the optical scanning of the fundus to obtain new data, and to form a new tomographic image of the fundus based on the new data was acquired.
7. —种眼底图像处理装置,其特征在于包括:存储元件,存储受检眼的眼底断层图像、及显示所述受检眼的眼球光学系统状态的光学信息;运算元件,根据所述光学信息来运算所述眼球光学系统的倍率;以及分析元件,包含计测位置设定元件,设定所述眼底的计测位置,且所述分析元件根据所述倍率来对所述断层图像进行分析,并求出由所述计测位置设定元件所设定的所述计测位置的所述眼底的层厚度。 7. - Species fundus image processing apparatus, comprising: a storage element, a tomographic image of the fundus of the examinee's eye is stored, and a display optical system of the optical information of the examinee's eye eyeball state; computing element, according to the optical information computes the eyeball optical system magnification; and analyzing elements, comprising a measuring position setting member sets the fundus measuring position, and the analysis element to analyze the tomographic image according to the magnification, and obtaining the fundus setting the measuring element by the position measuring position set by the layer thickness.
8.根据权利要求7所述的眼底图像处理装置,其特征在于,所述光学信息包括所述受检眼的角膜曲率、屈光度以及眼轴长度中的至少一个测定值。 8. fundus image processing apparatus according to claim 7, wherein the optical information includes the examinee's eye corneal curvature, refractive power and axial length of the at least one measured value.
9.根据权利要求8所述的眼底图像处理装置,其特征在于,所述光学信息包括眼内透镜信息,此眼内透镜信息显示所述受检眼内是否安装着眼内透镜,所述运算元件根据所述眼内透镜信息,判断有无眼内透镜,当判断存在眼内透镜时,代替所述屈光度的测定值,而根据安装在所述受检眼内的眼内透镜的度数,对所述倍率进行运算。 9. The fundus image processing apparatus according to claim 8, wherein the optical information includes intraocular lens information, lens information display is installed within the focus intraocular lens within the eye of the subject, said computation element according to the intraocular lens information, whether the presence or absence of intraocular lens, when it is determined the presence of the intraocular lens, instead of the measured value of the refractive power, the degree of intraocular lens mounted in the eye of the subject, on the said magnification operation.
10.根据权利要求7所述的眼底图像处理装置,其特征在于, 所述存储元件存储所述眼底的表面二维图像,所述分析元件在所述眼底的深度方向上对所述断层图像进行积分,形成积分图像,并根据所述倍率,对所述二维图像和所述积分图像进行定位,所述计测位置设定元件根据所述定位的结果,来设定所述眼底的计测位置,并根据所述断层图像,求出所述计测位置的所述眼底的层厚度。 10. The fundus image processing apparatus according to claim 7, characterized in that the surface of the two-dimensional image of the fundus of the memory element stores, analyzes the elements of the tomographic image in the depth direction of the fundus integral, the integral image is formed, according to the magnification, and the image of the two-dimensional integral image is positioned, said measuring position is set according to a result of said positioning member to set the measurement of the fundus position, according to the tomographic image of the fundus to obtain a layer thickness of the measuring position.
11.根据权利要求10所述的眼底图像处理装置,其特征在于,所述分析元件确定所述二维图像中相当于视神经乳头中心的位置,并将以所述经确定的位置为中心且具有预定半径的圆形区域设定为所述计测位置。 11. The fundus image processing apparatus according to claim 10, wherein said analysis element is determined that the two-dimensional image corresponding to the position of the center of the optic nerve head, and to the determined position of the center and having circular area of ​​predetermined radius is set to the measuring position.
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